Graft core for seal and suture anastomoses with devices and methods for percutaneous intraluminal excisional surgery (PIES)

ABSTRACT

Devices and methods are described for emplacing bypass grafts in any tubular tract in a mammalian body by natural or percutaneous entry and suturing intraluminally. A coronary bypass is used as the preferred embodiment. Prior art devices and methods for accomplishing this object are disclosed in patents but are not in use today. The prior art in use requires opening the chest so the surgeon can get his hands or tools in to manually tie ten or more sutures on each end of each bypass, each requiring a minute to tie. This produces extensive collateral damage to the chest, dangerously long heart stoppage, intensive care, excruciating pain and months of recovery. The devices of the present disclosure cause the patient no collateral damage, little discomfort, probably no more than overnight in hospital, and complete recovery within days. The devices are introduced percutaneously and advanced intraluminally by catheters with fluoroscopic, radiographic and other electromagnetic means of tracking through the body. A cutting device produces an opening in the aorta which is immediately clamped by a clamping catheter that inflates annular balloons on either side of the aorta wall around the opening. An explorer guidewire is advanced, with the aid of various tracking devices, through the opening and curved around the heart to the predetermined site of anastomosis on the coronary artery where the guide wire tip is emplaced. A delivery tube device, containing a natural or artificial bypass graft with graft core devices pre-operatively sutured to each end by hollow sutures, is advanced over the explorer guide wire. Template devices shape the ends of the bypass graft to optimally expose intimal layers for alignment those of the artery and aorta to improve the probability of rapid, healthy growth. The delivery tube device enters an opening as it is cut in the coronary artery by a cutting device mounted on its distal end. This briefly blocks the escape of blood while a push-rod device pushes the graft core out of the delivery tube. A brim section of the graft core, being released from its compressed state inside the delivery tube expands like a flange inside the coronary artery. This provides a leak-resistant seal between bypass graft and coronary artery while the push-rod device is fully inflated to align its rods with the stiff sutures inside the hollow sutures and pushes them through the edge of the tissue around the opening and into the brim section of the graft core flared inside the body tube. Barbs hold the stiff sutures in place. This suturing of bypass graft to aorta is accomplished with similar devices. A dozen sutures are emplaced simultaneously in less time than it takes to emplace one suture manually, thus reducing or eliminating use of a mechanical heart machine. This combination seal and suture anastomosis is logically more fluid-tight than one produced by manual suturing alone or seal alone. Eliminating collateral damage allows the known advantages of bypass grafts over stents to be realized in practice.

CROSS REFERENCE TO RELATED APPLICATIONS

Not Applicable

FEDERALLY SPOSORED RESEARCH

Not Applicable

SEQUENCE LISTING OR PROGRAM

Not Applicable

BACKGROUND OF THE INVENTION

1. Field of Invention

This invention relates generally to bypass grafts introduced intraluminally, specifically to anastomoses made fluid-tight by seal and suture cores.

2. Prior Art

A substantial percentage of elective surgical procedures involve joining tubes that are not joined naturally. The primary reason is that tubes carrying essential body fluids for circulation and excretion often suffer physiological damage or partial blockage. Such sites are bypassed with another tube joined to the damaged tube on both sides of the damaged site. The bypass tube may be extracted from elsewhere in the body, from a compatible body or made of artificial material. The tracts requiring a bypass include urethral, gastrointestinal, vascular, cerebrospinal, and fallopian as well as shunts for dialysis. The present invention provides a way of approaching and joining body tubes intraluminally without the collateral damage caused by cutting through bone, muscle and body sheaths, as is typical of prior art.

Of all tracts in the body, coronary arteries are most often bypassed by grafts. About 500,000 procedures are performed worldwide each year. This is because disease in coronary arteries is the leading cause of premature death in industrialized societies. The usual method of emplacing these grafts is by opening the chest and stopping the heart while a surgeon manually places tiny sutures to connect the ends of the graft tube to the wall around openings in the side of the coronary artery and in the side of the aorta. Opening the chest is painful, requires immediate intensive care and long recuperation. The risk of permanent mental disorientation from a stopped heart goes up sharply after an hour on the artificial pump. This collateral damage is just so the surgeon can get his hands in place to emplace sutures. Placing sutures manually takes a skilled surgeon about a minute per suture. About ten sutures are required for each end of each graft and a triple bypass involves three grafts, requiring a total of 60 minutes to emplace 60 sutures. If any sutures are too loose or too tight, blood will leak from them when the heart is started again. This can cause acute or chronic loss of blood pressure and possible scarring, which results in another blockage. Before the chest is closed additional sutures may be placed to stop the leakage.

In common medical usage the term “anastomosis” is used to refer to joining or grafting two tubular body parts that are conduits for a fluid. The term is derived from the Greek, referring to opening a mouth, originally to the mouths of river branches but used by early anatomists for all branching tubular body parts, including blood vessels and nerves. The term “side-to-side” is used to refer to anastomoses that join the cut sides of two tubes. The term “end-to-side” is used when the transected end of a tube is joined to the side of another tube. The graft is generally described as a body portion with a first end, a second end, and a lumen therebetween. The term “lumen” refers to the inside of the tube where some substance flows. Body tubes are also called conduits or vessels. Since conduits can be troughs and vessels can be objects floating on conduits, the term “tube” is used here.

To accomplish a coronary artery bypass graft (CABG) by prior art it is necessary to cut through the sternum and cause other collateral damage. The same bypass graft can also be emplaced by a different prior art of making openings in the chest to push through lights, cameras and other endoscopic devices. These procedures are known as MIDCABG and involve less collateral damage than CABG, but still represent a severe strain on patients. It is more difficult to manually place sutures through small holes with small lights and small cameras than it is through a large chest opening with bright lights and ability to move the heart so as to expose the target site for easier access. Therefore leakage is even more likely with a MIDCABG. In the event of leakage in MIDCABG, the field is too bloody to see where to place more sutures. The operation must immediately be changed into a full CABG to add sutures and stop the leak. Therefore the MIDCABG procedures have not replaced CABG procedures, except in a small percentage of cases, perhaps a few thousand a year. CABG will remain the gold standard until more compelling alternatives than the MIDCABG are found.

The CABG procedure for emplacing a bypass graft is undesirable because it creates extensive collateral damage to the body and adds risk of serious damage from the effects of long heart stoppage. The MIDCABG procedure creates less collateral damage but creates a more difficult and lengthy suturing process that too often requires a CABG procedure to fix the defective anastomosis.

Alternatives to Suturing

The disadvantages of manual suturing in CABG and MIDCABG procedures led to patent applications for devices to make the anastomosis more leak resistant or taking less time to emplace or both. Some such devices, made of metal or other hard substances that look like plumbing fixtures reached the market, but have been removed amid legal suits regarding leakage. Other devices are soft and pliable, being made of soft collagen or other flexible substances. They are intended to seal the graft connections by fluid pressure alone pressing against the flange of the seal device located inside the body tube. They have not been found to be effective or safe in trials with animals. To be more safe and effective than manual suturing they have to be more leak-resistant than manual suturing. Prior art shows no such pliable devices designed to be introduced intraluminally as are the pliable seals in the present application.

Three types of pliable connectors for use in CABG or MIDCABG applications are summarized here. One device by Akin, Conston, et al in U.S. patent application 2001/0044631, consists of two flexible sheets of material of any shape connected around the circumference of an opening near their center, deployed through openings in side-by-side lumens in each tube and held by fluid pressure inside each lumen. These devices are called “seals” in the patent application and were believed to be more fluid-tight and more quickly emplaced than suturing, but tests on swine demonstrated that the seals are not as leak-resistant as hoped. One embodiment uses adhesive for a tighter seal. The seals have not been demonstrated to be sufficiently leak-resistant to be used in humans. An associated device, described as a surgical dispenser, is used to hold the compressed flexible sheets while they are manually inserted through the side of body tubes. Use of these devices requires that the chest be fully or partially open.

Akin, Conston, et al in U.S. patent application 2003/0088256, describe a similar seal partially held in place by fluid pressure but supposedly aided by various configurations of support members deployed inside each lumen and in the opening between them. Again adhesives are included in one embodiment. This device is manually inserted through the sides of tubes through an open chest. An end-to-side version is shown in a figure. There is no evidence that this device is more leak-resistant than the previous one.

Spence, et al, in U.S. patent application 2004/0097992, describe a device composed of two flexible oval segments called “double cuffs.” They are intended to be pushed through openings cut in two side-by-side tubes and be held there in the lumens temporarily by fluid pressure. Metal spikes in the cuffs are then are pressed through the walls of the body tubes and into the metal oval opposite to accomplish a permanent connection. The metal remains in the body. The leak resistance is unknown. The chest must be opened to emplace the device. With this device there is no doubt regarding the temporary nature of the seal alone because an oval of malleable studded metal segments is used for the intended permanent connection.

It is evident that all these devices can be emplaced in less time than the approximately ten minutes it takes to manually suture one anastomosis. However they have not been demonstrated to be as leak-resistant as an anastomosis made by manually applied sutures. No record of their being used has been found except for the example with swine as noted.

Avoiding Collateral Damage.

So important is finding a way to avoid the serious collateral damage inherent in CABG procedures, that other patent applications have described ways of accomplishing the same bypass anastomoses with little or no breaching of the chest. To be successful these devices and methods must also provide anastomoses at least as leak-resistant as those produced by manual suturing. If they can be performed with little or no stoppage of the heart and be accomplished quickly, that is an added advantage to the 500,000 people who now tolerate CABG procedures each year.

Intraluminal Route to Heart

A route to the aorta and coronary artery that does not breach the chest is an intraluminal one through the femoral artery. Long catheters and fluoroscopic devices make it possible to select a point of entry to the body far from the coronary artery and track devices advanced from entry point to target. The site for entry is chosen where there are no interposing body parts between the skin and a large artery in the groin (or arm). This is called percutaneous in that only skin is punctured rather than cutting bone, muscle and natural protective sheaths like the pericardium. Originally the purpose of this method was to advance a balloon into the narrowed site. Inflating the balloon opened the narrowed coronary artery and avoided the need to open the chest for a bypass. But the artery snapped shut again in about 30% of the cases. A stent was invented to solve the restenosis problem. A stent is a tube of wire mesh that expands as the balloon is inflated and retains the expanded shape to keep the narrowed site open after the balloon is deflated and withdrawn. It was found that in a certain number of cases the arterial wall grew through the holes in the mesh stent, again closing down the flow of blood to the heart muscle. To prevent this growth the stent device is coated with a growth-inhibiting chemical that elutes into the artery over time. Different agents, originally intended to prevent the growth of cancer cells are used in different eluting stents.

Successive devices were patented and developed over time, while the general method is called Percutaneous Coronary Intervention (PCI) and its practitioners; cardiac interventionists. The original balloon technique was called Percutaneous Transluminal Coronary Angioplasty (PCTA). Since no surgery is involved, there is essentially no collateral damage with these methods. Though intervention was not originally intended to be used for surgical entry to the body, it can be used to emplace bypass grafts using new devices and methods.

An example of percutaneous entry and intraluminal advancement to the surgical field is shown by Makower in U.S. published patent application 2004/0073238, Device, System and Method for Interstitial Transvascular Intervention. It describes devices for percutaneous entry, intraluminal advancement to a desired location, opening of an artificial port to another blood vessel or organ, tumor, or other anatomical structure so that one or more operative devices can be advanced to perform the desired procedure. Mackower describes active and passive means for the interventionist to see the progress of devices along the intraluminal tract, such as the fluoroscopic tracking device most commonly used for tracking catheter-based systems. When the devices leave the highways of natural body tracts to venture outside the tracts they are likely to need even better tracking devices. Makower describes active and passive radiographic, fluoroscopic magnetic, sonographic, or other electromagnetic detection of the location of devices in the body. Use of these various known forms of energy for localization is obvious. Makower's device leaves the arterial tract by cutting openings in the coronary artery to enter the coronary vein running parallel to the coronary artery. The vein is converted to a bypass graft and terminated as a vein by tying off its ends from connection with the tract for returning blood to the heart. This is done through holes made in the chest. The use of this adjacent coronary vein is different from use of vein harvested elsewhere in the body. The vein commonly used in CABG procedures is the sapheneous vein from the leg, closer in size to the coronary artery than is the coronary vein. In addition to the small vein size, and the need to breach the chest, there is a more serious disadvantage that a triple bypass would require terminating all veins serving the heart. Makower makes the point that percutaneous entry and intraluminal advancement is applicable to other tracts in the body than vascular, and that the vascular tract is merely a conduit to other fields of surgery.

Implanting Bypass Grafts Intraluminally

Two other patent applications describe devices that use percutaneous entry and intraluminal advancement to accomplish bypass grafts without breaching of the chest. They describe devices for cutting or otherwise forcing openings, clamping openings, finding target sites using various tracking devices energized by various but obvious alternative forms of electro, magnetic, and mechanical energy, snaring guide wires to lead from aorta to artery and use of wire mesh and stents to make anastomoses with the aid of balloons to shape the wire mesh materials. Both applications indicate that grafts may be harvested from natural sources or be of artificial substances.

Goldsteen, et al, in Medical Grafting Methods and Apparatus, U.S. patent application 2004/0116946, and LaFontaine, et al in System and Methods for Percutaneous Coronary Artery Bypass, U.S. patent application 2003/0195457 advance a guiding catheter through the femoral artery to an exit site in the aorta and use a method of connecting the aorta and coronary artery target site by a single continuous guide wire. Both use a snare method to accomplish this but Goldsteen describes a device placed in the coronary artery to deflect the guide wire through the wall. Both snare this guide wire by a second loop of guide wire pushed through the wall of the aorta to draw the first guide wire back out the intraluminal route to constitute a continuous guide wire going through both sites of anastomosis. Goldsteen utilizes endoscopic fiber optic light advanced transluminally to illuminate and view the snaring operation. This is done a long time before the anastomosis is made so there may be time for blood to leak through the small holes made by the wire guide or for the holes to open wider. Goldsteen enlarges this opening by twisting through a threaded conical tip. Successively larger catheters are twisted and pushed though the opening until the largest, the guiding catheter, is pushed through. The problem of preventing loose tissue fragments, produced by this grinding action, from entering the blood stream is not addressed. The guiding catheter has a pair of annular balloons that are inflated on either side of the opening to clamp it. It appears from the figures that the inflation lumens for these balloons are coincident with the catheter wall and if so, the device has no means of inflating the clamping balloons. Furthermore the balloons press directly on the intimal growth layer of the wall creating the potential for injuring this and other layers.

LaFontaine has one embodiment where the heart is stopped and another where it is not. He utilizes a vacuum device to isolate and stop blood flow before cutting through the aortic wall. This device may avoid injury to the intimal layers of the wall but it is unwieldy and a potential source of dangerous suction inside the aorta if it comes loose from the wall it adheres to by suction. No indication is provided about the size of cut in the aorta wall but after it is made an everted graft mounted on a coupler is pushed (bare) through the opening where it is reverted to outside out as it travels though the pericardium on the wire between aorta and artery. The disadvantage is that graft will be injured by turning it inside-out and injured again by turning it back again. Several electro, magnetic, mechanical devises in addition to radiopaque markers for tracking and locating the graft end are described. These forms of energy are typically used for tracking purposes and their use in this application for that purpose is obvious. LaFontaine describes how, after the reverted graft is pushed over the guide wire to the site of anastomosis on the coronary artery, another cut is made to allow the graft inside the coronary artery where it is aligned coaxially with the artery. This coaxial alignment places the inner, epithelial layers of the graft and artery separated by the full thickness of the graft. These intimal layers must be in contact for optimal growth so it is a severe disadvantage that they are separated by this alignment. A short cylinder of wire mesh surrounding a balloon is advanced through the graft and expanded to the circumference of the artery to hold the coaxially aligned graft and artery together. The likelihood that this is insufficient to keep the graft in place is shown in an alternative embodiment that provides a short cylinder of adhesive to hold the graft in place. This adhesive cylinder has the disadvantage of creating yet another barrier between the intimal layers of graft and artery to inhibit growth. How blood is kept from leaking into the pericardium while this lengthy process is performed, is not explained, but even a drop of leaking blood is a serious problem. The graft is attached to the aorta in a similar manner with the same disadvantages. Variously shaped wire mesh, stent-like devices and balloons to push them into place to keep the graft attached to artery and aorta are described, each showing disadvantages of the types noted here.

Goldsteen utilizes radiopaque markers and orthogonal fluorescent screens to track and display location of an artificial graft conduit as it moves mounted on the outside of a catheter through the pericardium on the guide wire. These are the conventional means of tracking devices being advanced through catheters inside body tubes and therefore continuing to use these same means to track devices between lumens is obvious. The artificial conduit used in one application is a stent-like wire mesh with interstices filled with artificial graft material. After one of several versions of a threaded or barbed tip cuts or grinds its way through the artery wall, the artificial graft is advanced through the opening and its wire ends sprung radially inside the artery lumen. In case these do not make good contact a balloon is inflated in the opening to adjust them. This process is repeated at the opening in the aortic wall with rings of barbs on either side of the wall. If the contact requires adjustment by balloons the blood will be leaking from the opening into the pericardium while the balloon is delivered to site and manipulated to correct the imperfect connection. In another embodiment a natural graft is implanted rather than the artificial one by placing the natural graft inside the artificial graft for delivery. The natural graft is attached after the artificial graft is attached. This has the disadvantage of twice pushing rings of metal barbs through both sides of the tube wall by balloons. The damage to delicate tissue must be even greater than caused by attaching the first artificial tube. In still another embodiment the natural graft is not preceded by the artificial graft. These devices appear to injure tissue in the process of advancing the graft and in making the anastomosis as well as failing to provide intimal contact between layers of the tubes being joined that are the primary agents for growth between tubes. In addition the irritation of repeated driving of metal barbs though the frail coronary artery walls makes leakage more likely and inhibits growth at the junction. The need to doubly insult the tissue of the graft by eversion and reversion as it is pushed from aorta injures the graft tissue along its entire length as well as at its ends. Placing the graft concentrically within the artery to which it is to be joined insulates the intimal growth layers by the thickness of the graft making growth difficult if not impossible. The lengthy process of manipulating wire mesh with balloons of various sizes and shapes to produce an anastomosis does not appear to be as fast as manual suturing and does not provide as sure a connection, i.e. as leak resistant as manual suturing. In short, while these methods appear to avoid all or most of the collateral damage of CABG and MID-CABG procedures, they have their own disadvantages including damaging tissues and lack of a device for making an anastomosis at least as good as achieved by manual suturing.

A successful alternative to CABG and MIDCABG procedures must not only avoid the collateral damage of those methods, but also avoid the disadvantages of the devices discussed here, and provide an anastomosis that is at least as good as that produced by manual suturing with CABG procedures. If, in addition, a new alternative is capable of providing a more fluid-tight anastomosis with better growth potential than that provided by a surgeon in a CABG or MIDCABG procedure, no advantages remain for those older procedures.

Emplacing stents will remain as an effective treatment for one or even two coronary arteries. However with two or more severely narrowed arteries, bypass grafts are the only option.

A successful percutaneous intraluminal method of emplacing bypass grafts would benefit a large number of patients who need bypass grafts but cannot sustain the more invasive surgical procedures as well as the 500,000 or so who now tolerate CABG procedures each year.

BACKGROUND OF THE INVENTION—OBJECTS AND ADVANTAGES

Accordingly, several objects and advantages of the invention are:

1. To provide devices that allow percutaneous entry and intraluminal advancement to a chest graft bypass site, thereby avoiding all collateral damage caused by entry through the chest.

2. To provide devices and methods for improved anastomoses.

3. To provide a core device to accomplish a seal in an anastomosis between a graft and a body tube, thereby preventing leakage until suturing is accomplished.

4. To provide the core device with sutures to accomplish a combination seal and suture anastomosis, thereby improving leak resistance over prior art of suture alone or seal alone.

5. To provide devices for pushing all stiff sutures in the core device simultaneously, thereby completing the suturing of the anastomosis in a short time without need to stop the heart.

6. To provide sutures on the core device to accomplish suturing the graft to the core device before the operation starts, thus accomplishing most of the suturing under ideal conditions and so this suturing does not need to be done within the body during the operation.

7. To provide improved sutures that interact with other devices to achieve the objects of accomplishing suturing quickly and effectively during the procedure.

8. To provide devices that compress the cores on each end of the graft for insertion in a delivery tube that provides intraluminal transit, thereby avoiding injury to the graft and quick insertion into the target lumen.

9. To provide anastomosis devices for clamping the aorta wall at some distance from an opening made in the wall, thereby avoiding injury to the intimal layer that prior art clamping causes by direct pressure on the intimal layer of the cut.

10. To provide anastomosis devices for making openings in the sides of the same circumference as that of the graft being anastomosized to provide intimal contact of growth layers, resistance to leakage and, in the case of an artificial graft, optimal contact between openings of the intersecting tubes.

11. To provide devices for preoperatively cutting a bevel and shape on the end of each graft that ensures good contact between intimal layers of graft and tube, thereby aiding fast growth.

12. To provide devices for placing sutures without the use of needles, thereby causing less trauma to frail arteries than a needle larger than the sutures used in prior art manual suturing.

13. To provide anastomosis devices for tracking and locating target areas and aligning cutting blades with a longitudinal axis of tube to be cut with the aid of fluoroscopic, radio frequency, and other transmitting/receiving devices, thereby providing greater assurance of cuts being made properly at the desired locations.

Further Objects and Advantages are:

14. To provide the clamping balloon devices with oversize lumens for carrying a volume of inflation fluid that quickly inflates and deflates the balloons, thus minimizing the time for blood to flow out of the aorta.

15. To mount cutting balloons on catheters such that the catheters enter the openings as they are made, thus preventing blood from escaping the coronary artery until the core seal and sutures can put in place.

Yet further objects and advantages will become apparent from a consideration of the ensuing description and the accompanying drawings.

SUMMARY

In accordance with the preferred embodiment of the invention, a core device is attached to each end of the bypass graft by hollow sutures clipped to posts and a circle of sutures to make a secure connection. The graft ends have been preoperatively cut on a template device to the proper angle and shape for optimal exposure of the intimal layers to the same layers on the tubes to which they will be joined. The operation begins by percutaneously introducing and transluminally advancing a clamping catheter with twin annular balloons on the end to the site of anastomosis in the aorta. As this catheter pushes a cutting balloon through the aorta wall, the distal balloon is inflated outside the aorta to press against the annular balloon already inflated inside the aorta, thus clamping the opening cut in the wall. One or a combination of tracking devices are used to track an explorer guide wire as it is pushed through the opening and the pericardium to find the target site of anastomosis on the coronary artery and attach itself. Over this guide wire the tube delivering the prepared graft and core devices is advanced. A cutting balloon on its end makes a slit in the coronary artery that the delivery tube is pushed into and briefly serves as a plug to keep fluid from escaping from the coronary artery. It is then pulled back while the core device is pushed forward, thus allowing the compressed brim of the core to expand inside the artery. The brim is flexible and in the shape of the body tube in which it is located thus temporarily sealing the opening. A device with a plurality of rods equal to the number of stiff sutures in the core pushes the stiff sutures simultaneously through the tube wall and into the brim. This quickly completes the combination seal and suture anastomosis that must be more fluid-tight than either alone. The anastomosis on the other end of the graft is completed in a similar manner at the aorta, completing one bypass graft by percutaneous, intraluminal means. Additional grafts for double or triple bypass are conducted the same way with either no need to stop the heart or only for seconds.

DRAWINGS—FIGURES

FIG. 1 shows two tubes joined by a graft, the product of prior art and the product of this preferred embodiment being accomplished by different devices and methods creating different amounts of collateral damage.

FIG. 2 a shows a preparation bench on which a graft is prepared and attached to graft core devices on both ends prior to the operation.

FIG. 2 b shows a cross-section of the graft mounted on a cutting sleeve for preparing the size and shape of the ends of graft.

FIG. 3 a shows a graft core comprising a stem and a brim.

FIG. 3 b shows the graft core with two hollow sutures inside the stem and posts snapped on the hollow suture ends with a segment of a circular suture connecting the posts.

FIG. 3 c shows the relationship of hollow suture and stiff suture with the posts and a circular suture segment.

FIG. 3 d shows the graft core with posts, hollow sutures and a circular suture ring on the preparation bench with the graft coming out of the delivery tube ready to be mounted on the stem of the graft core.

FIG. 4 a shows a device for snapping together the posts and hollow sutures.

FIG. 4 b shows the compression tweeze device for compressing the brim of the graft core and the brim being pushed into a delivery tube device.

FIG. 4 c shows the cross-section of a prepared graft sutured by hollow sutures and posts to the stem of a graft core at the 6 and 12 o'clock positions for which an angle of intersection and a tangential angle are seen to be equal.

FIG. 4 d shows the same elements as shown in FIG. 4 c at the 3 and 9 o'clock positions, where the ends of the hollow sutures must point the stiff sutures back toward the stem's longitudinal axis in order to intersect the brim at these positions.

FIG. 4 e shows the same elements as FIG. 4 c but at the 4 and 10 o'clock positions.

FIG. 4 f shows a push-rod balloon with rods extended distally and proximally.

FIG. 5 a shows circular excision device with conical dart.

FIG. 5 b shows a cylindrical cutting arm device.

FIG. 5 c shows the cylindrical cutting arm device mounted in a catheter.

FIG. 5 d shows a tracked slitting device with three views of a microtome blade mounted in a cart as the cart is pulled to successive positions along a track.

FIG. 5 e shows a circular push-blade cutting device.

FIG. 5 f shows a deflated tubular push-blade cutting device mounted on a holding balloon.

FIG. 5 g shows an inflated tubular cutting device with blade exposed and mounted on a holding balloon.

FIG. 5 h shows the tubular push-blade device deflated, folded and ready for withdrawal.

FIG. 6 a shows the end of a clamping catheter with deflated annular clamping balloons and a dual channel for inflation fluid made by a double wall.

FIG. 6 b shows clamping balloons inflated and exhibiting radiopaque markers.

FIG. 6 c shows a cross-sectional view of one semi-inflated clamping balloon.

FIG. 6 d shows a cross-sectional view of a deflated clamping balloon.

FIG. 7 shows an explorer guide wire with screw tip and radiopaque longitudinal marker.

FIG. 8 shows a target guide wire with longitudinal radiopaque marker.

FIG. 9 a shows the explorer guide wire with transmitting tip and the target guide wire with a receiver tip.

FIG. 9 b shows a transmitter on the tip of the explorer guide wire and a delay line to a second transmitter proximal to the longitudinal marker and the target guide wire with two receivers and delay line between them.

FIG. 9 c shows two transmitters on the target guide wire and four receivers on the delivery tube.

FIG. 10 a shows a holding balloon with embedded tubular cutting device and the explorer guide wire.

FIG. 10 b shows the inflated tubular push-blade device with blade exposed.

FIG. 10 c shows the deflated push-rod balloon close to the stem of the graft core.

FIG. 10 d shows a view of the inflated push-rod balloon entering the graft core with a key and a keyway aligned.

FIG. 11 a shows the relationship of a cross-section of the graft tube and the wall of a second body tube with the graft core, posts, hollow sutures and stiff sutures in a completed anastomosis.

FIG. 11 b shows the same anastomosis as shown in FIG. 11 a from a different view.

FIG. 12 a shows the graft core device and a plane erected at 90 degrees to the tangent to the stem at the point of erection thus forming a tangential angle between stem and brim at that position on the stem.

FIG. 12 b shows the same erected plane tangent to different position on the stem and the tangential angle at that point.

FIG. 12 c shows the plane and the tangential angle at another position on the stem.

FIG. 12 d shows the plane and the tangential angle with cross-sections of two different grafts of different thicknesses which illustrates the longer distance the stiff suture must travel for greater thicknesses of graft and also how the stiff suture must be pointed back toward the target point on the brim for obtuse angles.

DRAWINGS—REFERENCE NUMERALS

-   1. First Tube -   2. Second Tube -   3. Graft -   4. Graft end 4 -   5. Graft end 5 -   6. Preparation Bench -   7. Cutting Sleeve -   8. Support Bracket -   9. Slot -   10. Delivery Tube -   11. Rest -   12. Graft Core -   13. Mark -   14. Sleeve Base -   15. Guiding Groove -   16. Hypodermic Needles -   17. Measurement Marks -   18. Stem -   19. Brim -   20. Junction -   21. Angle -   22. Outside Surface (Brim) -   23. Inside Surface (Brim) -   24. Outside Surface (Stem) -   25. Hollow Sutures -   26. Post -   27. Stiff Suture -   28. Hollow Cone -   29. Circular Suture -   30. Compression Tool -   31. Push-rod Balloon -   32. Rods -   33. Push-rod Catheter -   34. Key -   35. Circular Excision Device -   36. Circular Microtome Blade -   37. Excision Balloon -   38. Cruciform Conical Arrow -   39. Guidewire (Arrow) -   40. Cylindrical Slicing Device -   41. Cylinder -   42. Blade Arm -   43. Radiopaque Marker -   44. (Pulling) Guide Wire -   45. Pulleys -   46. Spring -   47. Support Rod -   48. Slot -   49. Tracked Slitter -   50. Track -   51. Tunnel -   52. Moving Element -   53. Swivel Blade -   54. Axle -   55. Guide Wire -   56. Pin -   57. Bar -   58. Lever -   59. Pulley -   60. Pulley -   61. Hinged bar -   62. Receptacle -   63. Hinge -   64. Push Blade Balloon -   65. Non-Compliant Body -   66. Compliant Extender -   67. Microtome Blade -   68. Push Blade Balloon -   69. Holding Balloon -   70. Clamping Catheter -   71. Clamping Balloon -   72. Clamping Balloon -   73. Double Wall -   74. Divider -   75. Radiopaque Marker -   76. Curved Member -   77. Straight Portions -   78. Holding Balloon -   79. Explorer Guide Wire -   80. Screw Tip Guide Wire -   81. Opaque Marker -   82. Target Guide Wire -   83. Longitudinal Opaque Marker -   84. Receiver Tip -   85. Receiver Tip -   86. Time Delay Line -   87. Receiver -   88. Time Delay Line -   89. Receiver (12) -   90. Receiver (6) -   91. Receiver (3) -   92. Receiver (9) -   93. Distal Opening -   94. Lip -   95. Keyway -   96. Plane -   97. Tangential Angle -   98. Graft Cross Section (1) -   99. Graft Cross Section (2) -   100. Miter Angle -   101. Electromagnet

DETAILED DESCRIPTION—PREFERRED EMBODIMENT—FIG. 1—GRAFT

As is well known by those skilled in the art of percutaneous coronary intervention (PCI), the devices, pharmaceuticals, and methods for accomplishing PCI are described in numerous publications, e.g., The Interventional Cardiac Catheterization Handbook by Morton J. Kern, second edition, 2004, Mosby, Elsevier Inc. To the extent appropriate, devices, methods, pharmaceuticals and general knowledge from such sources as describe the state of the art are applicable to the present devices and methods in various application situations. Things that are appropriate vary with the application. For instance heparin, nitroglycerin, and certain other pharmaceuticals, appropriate in a homeostatic application would not be appropriate in an application to the fallopian tubes or the colon. However catheters are usable in all applications.

FIG. 1 shows a graft anastomosized according to the present invention. It is visually and functionally the same as that of prior art in that the sides of a mammalian first tube 1 and second tube 2 are connected by the transected ends of a graft 3. The transected ends of the graft are identified as 4 and 5. The present devices achieve this product without causing the excessive collateral damage typical of prior art, with greater safety and lower probability of undesired side effects and with higher probability of resistance to leakage, quality, and speed of healthy growth.

FIG. 2 a shows a preparation bench 6 used prior to the operation to cut the graft to the desired length and circumference, shape the ends for optimal contact with the body tubes, and cut and mark holes for the entry of hollow sutures when the graft is placed on the graft core device.

The length of the bench as shown is somewhat shorter relative to its actual width in order that both ends can be seen clearly in one figure. The bench must be securely fastened to a stable table. A cutting sleeve 7 is mounted on a support bracket 8. The support bracket is movable along a measured slot 9 with measurement marks 17. This provides the means for accurately cutting the graft to the correct length. One cutting sleeve 7 provides the means of making end 5 of graft 3 the correct circumference and shape for joining to the first tube (aorta). The first and second tubes are often of different size and this is especially true of the aorta and coronary artery. The other cutting sleeve is for other end 4 and second tube 2 (artery) and produces a slightly different shape of the intersection of two tubes where the graft is only slightly smaller than the artery. The two junctions are complex three-dimensional oval curves that are a function of their sizes and the angle at which they are to be joined. A rest 11 for delivery tube 10 is shown along the center of the bench. Graft 3 is placed inside delivery tube 10 before its ends are sutured to graft core 12. A graft core is shown mounted on the other support bracket. The cutting sleeves are removed and replaced by graft cores 12. The cutting sleeve and graft cores are the same dimensions and so fit on the same supports.

FIG. 2 b shows a detailed view of a cutting sleeve 7 of the correct circumference, with cutting groove 15 for cutting the ends to the proper shape, hypodermic needles 16 for cutting and marking the entry points for hollow sutures on the graft when the graft is later mounted and sutured. The basis for selecting the sleeve with the correct outside diameter is estimating the diameter of the smaller of tubes 1 and 2 and subtracting (about) twice the thickness of the wall of the graft. One end of graft 3 is drawn up to mark 13. Graft 3 is shown only in cross-section as a white space at the top and bottom of the sleeve so the elements of the sleeve can be viewed. To avoid problems of fluid flow, the size of the opening in the first tube must be the same size as the opening made in the second tube and equal sized graft ends. To make the larger end of the graft the same diameter as the smaller end, a cut is made with a scalpel on the longitudinal axis of the graft from mark 13 to the sleeve's base 14. Folding the cut sides of the graft together, another (almost parallel) cut is made such that the two sides come together evenly. This is done so the end of the graft will fit snugly (without pulling) around cutting sleeve 7. Slitting the graft during preparation allows the circumference of the two graft cores to be the same—the same size as the stems which are the same diameter and also makes manipulation of the ends easier.

On the sleeve is shown a guiding groove 15. The groove is a template for inserting a scalpel and guiding it along the groove. Groove 15 is in the shape made by the intersection of two cylinders at the angle the physician intends to use in the application. The internal angle of the groove continuously varies along its sinuous path. It guides the scalpel to cut an acute bevel on the graft. This bevel is cut back from the innermost layer of the graft to the outermost layer in order to expose the inner layer without outer layers overlaying it. This acute angle varies for every point on the junction and is one-half the tangential angle between graft and tube at that point. This tangential angle may be determined by erecting a plane at a right angle to the tangent at a given point on the junction. This plane will intersect graft and tube to display the angle between them.

The miter angle between graft and tube is one half the tangential angle. It provides half the space for the graft end and half for the wall of the open tube. In this way the intimal layers of graft and tube are exposed to each other around the circumference of the anastomosis.

The shape is that of the junction of two intersecting cylinders with a bevel inclined back from the innermost layer to the outermost layer of the graft. This optimally exposes the innermost endothelial layer to the same layer on the body tube to which the graft will be joined.

The innermost endothelial linings of two tubes, called intima, should be in contact all along their circumference for a graft to grow quickly and properly. In some prior-art applications this was ignored, thwarted by inadvertent or intentional separation of endothelial layers, or, at best, left to a surgeon's imprecise scissors snip. The shape and angles imposed by this guide are more complex than can readily be made freehand with a scalpel or a scissors.

Short hypodermic needles 16 are pushed by a lever mechanism through holes in the sleeve and on through graft 3. A vacuum may be introduced through the needles in situations where greater precision is desired. With or without a vacuum, the preparer anticipates and coordinates this action with use of a sponge for pressing graft 3 gently against hollow needles 16 as they emerge and pass through the graft 3. The needles deposit a small amount of marker dye so the locations on graft 3 will be apparent when the graft is mounted on graft core 12. The number of hollow needles 16 varies with the application, but for convenience the number twelve will be used here for illustration. The spacing of the needles can also be varied. For instance two may be close together with a larger space to the next one, etc. For convenience of discussion these twelve will be evenly placed at the twelve clock positions.

At the other end of the bench the other end of graft 3 is on a cutting sleeve 7 that has a groove based on the junction between that end of the graft and the tube to which it will be joined. At this step the graft is measured for the exact length desired. Supporting bracket 8 for cutting sleeve 7 is mounted in a slot 9 where it can be moved back and forth and locked in place at a measurement mark 17 that reads the distance between guiding grooves 15 on the two sleeves. This end of the graft is drawn so it is without kinks but not tight and placed on the other cutting sleeve, as the preparer sets the desired length on measurement mark 17 of slot 9. It is the distance between the sites chosen for anastomosis on the first and second tubes and must not be too long or the graft will form kinks that inhibit flow, or so short that graft 3 will not reach or be somewhat stretched between the selected sites. The desired sites and length are determined by ultrasound or other devices prior to preparation. The scale on slot 9 provides that the desired length is the length actually cut. When the cutting process is completed on the second sleeve, one cutting sleeve 7 is removed from its mounting bracket and graft core 12 put on that support bracket 8. Since all devices are sized to work together, the graft core has the same inside diameter as the cutting sleeve and fits on the support bracket in the same position.

FIG. 3 a shows the details of graft core 12, comprising its stem 18 and brim 19, tangential angles between stem and brim, rules of thumb for sizing components and putting together a coordinated suite of sizes in a kit for a particular application, and how a combination seal by the brim and suturing to the brim produces a more fluid tight anastomosis than suturing or sealing alone. A junction 20 between stem 18 and brim 19 is a complex curve created by the intersection of two cylinders and matches the size and shape of guiding groove 15 on cutting sleeve 7. An angle 21 at which the longitudinal axis of stem 18 intersects the longitudinal axis of brim 19 may be at any angle. In certain application situations, e.g., a CABG, surgeons prefer angles between thirty and forty-five degrees (plus or minus). Each possible angle of intersection 21 produces a different complex curve for junction 20 and a different set of tangential angles between the stem and brim at each point around the junction. However, it is cumbersome to show figures with several angles 21 and a set of tangential angles for each. So forty-five degrees will be used to mean any number, plus or minus from that. The tangential angles at the representative clock positions will be used as illustrative of all such angles. Each application situation has tubes of characteristic dimensions, but the relationship of the dimensions of the suite of devices in the preferred embodiment remain (approximately) the same.

An outside surface 22 of brim 19 has the curvature and dimensions of the lumen of the tube into which it is to be placed to create a seal. The lumens of body tubes have deviations from being perfect cylinders for various reasons. And the brim may deviate from a perfectly smooth surface if it is found advantageous to place a small trench and bump to catch stiff sutures that enter the brim at very oblique angles. Whether this ‘imperfection’ in the surface would promote a blood clot is not known but is unlikely as the stiff suture in the trench will tend to create sufficient surface tension to keep fluid from entering the trench. So, while perfection is not possible, certain rules of thumb are followed to make the fit as good as practicable.

For instance, in the case of a lumen of 3.5 millimeters in diameter the curve of outside surface 22 of brim 19 has a radius of 1.75 in millimeters. The rule of thumb for the thickness of the brim is about ten percent of the diameter of the lumen of the smaller of tubes 1 and 2. Thus the brim which is to be placed in the smaller lumen of 3.5 mm would have a thickness of about 0.35 mm. That thickness makes the radius of curvature of inside surface 23 of the brim about 1.05 mm. That is 1.75 mm minus two times the 0.35 mm. thickness, i.e., 1.75-0.7=1.05. Stem 13 has an outside surface 24 with a radius about equal to the inside surface 23 radius of the brim 19 and a thickness about the same as that of the brim (0.35 mm in this example). In addition the brim is flexible and thus adjusts its shape to that of the lumen for a seal that is at least temporarily a good one. When sutures enter the brim and draw it into tighter contact with the lumen, the resulting flexible seal is better than can be achieved by pressure from the fluid alone (as with seals in prior art) and-the sutures add at least as much leak-resistance as manually placed sutures. The combination must be more leak resistant than either alone.

The radius of outside surface 22 of brim 19 is selected to have the curvature of the radius of the lumen in which it will be placed. But stems 18 of graft core 12 will be the same size for the first and second (usually smaller) body tubes. The thickness of stem 18 and brim 19 is the same or similar for both graft cores. If the lumen of first tube 1 is several times the diameter of second tube 2, the radius of curvature of that brim is fairly flat with respect to the curvature of the brim that is lodged in the smaller lumen. This is the case in a situation where the second tube is a coronary artery and the first tube is the ascending aorta. The exact sizes of the two tubes to be joined will vary by application but the size relationships should be considered as useful rules of thumb for sizing a package or kit of coordinately sized devices for a given application.

FIG. 3 b shows a view of the sutures inside and attached to graft core 12 and illustrates the relationships of sizes, angles, orientations and positions of graft core components. The base of graft core 12 is shown open so two of the (nominally) twelve hollow sutures 25 inside the stem can be seen. One end of each of hollow sutures 25 is at the base of the graft core: The hollow sutures are in line with the longitudinal axis of the stem until making a forty-five degree turn perpendicular to the longitudinal axis to come out of the stem radially at a certain angle and distance from junction 20 of the brim and the stem. This distance is a function of both the tangential angle between the stem and brim and the thickness of the graft. The angle at which the hollow suture exits the stem can be any acute angle, but 45 degrees and 30 degrees are used as examples. The thickness of the graft affects how far the lip of the brim should be extruded beyond the stem as well as the length of the stem. These relationships are described in a later paragraph along with illustrative tangential angles between brim and stem.

These tangential angles are determiners of how far each stiff suture must be driven to enter the brim, along with the thickness of the graft. The perpendicular distance between the surface of the stem and the end of hollow suture 25 is slightly more than the thickness of the graft so the hollow suture end will extend slightly beyond the graft. The two hollow sutures shown here represent the nominal twelve that are located at the clock positions. The 6 o'clock position is in the “heel” and the 12 o'clock position the “toe,” using the “foot” analogy as commonly used in CABG procedures to refer to a graft (leg) joined at an angle to a body tube (foot). Each hollow suture 25 will be placed in one of the dye-marked holes previously cut in the graft by hypodermic needles 16. The ends of the hollow sutures that come out of the surface of graft 3 are all at the same distance from the junction 20.

There is a post 26 for each hollow suture. The length of the post depends on the thickness of the graft and the acuteness of the tangential angle between brim and stem at the point on the junction where the post is placed to meet its corresponding hollow suture. The opening at the end of each hollow suture 27 is oriented toward the brim. The exact orientation is a function of the angle between brim and stem.

FIG. 3 c shows an exploded view of two types of sutures that are normally fitted one inside the other, hollow suture 25 and stiff suture 27. The posts 26 that are snapped on the ends of the hollow sutures to accomplish the suturing of the graft to the graft stem are shown. The means of moving the stiff sutures out the ends of the hollow sutures and size relationships that affect the distance each stiff suture must travel to reach its target on the brim are explained. It is also shown how one segment of circular suture 29 is connected to the end of the post.

Stiff suture 27 is slidingly fitted inside hollow suture 25. Post 26 is manually pressed and snapped on the end of hollow suture 25. The post and hollow suture constitute a complete suture holding the graft to stem 18. Hollow cone 28 flares from the base of each hollow suture 25. The stiff suture is shown outside the hollow suture, but in practice it is located inside the hollow suture. When a metal rod (not shown in this figure) of slightly smaller diameter than stiff suture 27 is introduced into the hollow cone 28 at the base of the graft core it rests against the stiff suture 27. Pushing the rod while holding the graft core 12 drives the stiff suture out the end of hollow suture 25 through the wall of tube 1 or 2 and into brim 19. Suture 27 is barbed so it will not retract once driven forward. The barbs are lodged in brim 19 and in the hollow suture 25. The length of the driving rods is such that they drive the stiff sutures the correct distance for entering the brim. Or the driving rods may be made the same length and the length of stiff sutures adjusted to be the correct length to travel into the brim. These operations are introduced at this point to aid in describing graft core 12. One segment of circular suture 29 is shown attached to the post.

FIG. 3 d shows one end of the preparation bench 6 with graft core 12 mounted in place of the cutting sleeve. For purposes of illustration the end 4 looks like it has been allowed to hang out of delivery tube 13 with the slit showing. The preparer normally places the end of the graft directly on the graft core after the sleeve is removed from support arm 8. The preparer wraps end 4 around stem 18 of graft core 12. The slit enables the preparer to slip one hollow suture 25 at a time through the dye-marked openings in graft 3 as end 4 is wrapped around stem 18. Hollow sutures 25 are shown emerging from stem 18 and posts 26 are shown coming from the junction with rings on their ends for snapping onto the hollow sutures thereby tying together their ends. At the time of manufacture the posts are connected by circular suture 29 except for one or more open link(s). The open link(s) allows the circular suture to be pushed away from interfering with the manipulation of hollow sutures and posts but are clipped together when they can be put in place.

FIG. 4 a shows the post with ring snapped on the hollow suture by a snapper device and the circular suture joining the posts. This gives the appearance of a wheel and spokes.

The purpose of the circular suture is to stabilize the location of each hollow suture and to prevent the individual hollow sutures from being forced backward when the stiff sutures are driven forward from the ends of the hollow sutures through tissue and brim. As the stiff sutures all push through the wall of the tube being anastomosized to the graft, there is-considerable back pressure on the ends of the hollow sutures from which the stiff sutures issue. Circular suture 29 will not increase in circumference and so tends to prevent the hollow sutures from backing up.

The hollow sutures and posts are manufactured so the exit point of each hollow suture is pointed at the outer circumference of the brim. At certain clock positions there is an inward bend to make the stiff sutures in the hollow sutures point at their target on the brim.

FIG. 4 b shows compression tool 30, used to compress the brim of the graft core. After one graft core is sutured to the graft and the slit in the graft sutured shut manually, the preparer uses compression tool 30 to compress the brim and push it inside the delivery tube (still on its rest on the bench) far enough that the other end of the graft hangs out the other end of the delivery tube. After the process of suturing graft end 3 to another graft core is accomplished, another compression tool 30 is used to compress that brim. The two compression tools are used to manipulate the two graft cores to be at the ends of the delivery tube with the graft loosely stretched between them.

FIG. 4 c shows a cross-section of graft 3 mounted on stem 18 and held by hollow sutures 25 and posts 26. The relationships of angles these elements bear to each other are defined and described.

The angle of intersection of the longitudinal axes of stem 18 and brim 19 is 45 degrees as seen in the angle at the bottom of the figure (the 6 o'clock position). The complement of 45 degrees is 135 degrees, as seen between the stem and brim at the top of the figure (the 12 o'clock position). At the 6 and 12 o'clock positions the tangential angles are the same as the angles of intersection. One half of the tangential angle is the miter angle. The end of the graft is cut to this angle by the guide on the cutting sleeve and is shown cut to that miter angle in the figure. The miter angle is also the angle of the post, as likewise seen in the figure. The miter angle leaves an equal amount of space for the wall of the tube as it folds around the brim and therefore an (approximately) equal amount of wall tissue for the stiff suture to cut through on the way to the brim. The hollow suture is shown emerging from the stem at an angle of 45 degrees. This angle could be some other value but 45 degrees but it must allow a proper “bite” of graft tissue to be caught in the triangle between hollow suture, post and stem. The graft is thus sutured to the stem under ideal access conditions during the preparation. All that remains to complete the suturing during the operation is pushing the stiff sutures from the hollow sutures through the wall of the tube and into the brim.

FIG. 4 d shows a cross-section of the graft on the stem at the 3 and 9 o'clock positions. The relationships of angles these elements bear to each other are defined and discussed for these positions.

At these positions the angle of intersection and tangential angles are different. The tangential angle between stem and brim is about 167 degrees at these positions. The miter angle is half the tangential or about 84 degrees and the graft is shown as cut to that angle by the guide on the cutting sleeve. The post emerges from the junction at that angle and the hollow suture is shown emerging at 45 degrees. In order to intersect the brim, the angle at which the stiff suture emerges from the hollow suture is also about 84 degrees back toward the longitudinal axis of the stem.

FIG. 4 e shows the 4 and 10 o'clock positions for the same elements. In these positions the hollow sutures point the stiff sutures approximately in line with the longitudinal axis of the stem.

Fabrication Materials

The graft core is fabricated from biodegradable material if the anastomosis stoma is to be live or biocompatible material if the graft core and graft are to remain in the body permanently. Suitable biodegradable substances are certain collagens, sugars, hydrogels, lactides and other material known to have a certain period for absorption by the body (resorbtion). Biocompatible materials include certain polymers, elastomers and silicones. The sutures of the graft core may be of the same or similar material, but of different characteristics.

The hollow sutures are bonded inside the body of the stem ending at the base of the stem and may be made of a slightly harder material than the stem to facilitate the smooth forward movement of the stiff sutures inside them, but not so hard that the barbs on the stiff sutures will not engage. The stiff sutures are made of a still harder and stiffer form of the same biodegradable material as they must puncture the brim as well as the walls of the first and second tubes. The material for stiff sutures must bend sufficiently as to bulge slightly if the tube in which the graft core is lodged moves with the beat of the heart. The entire core, brim and stem will move with the beat, but the brim may be affected first and thus the need for a slight bending of the stiff suture until the stem follows. The ends of stiff sutures must retain a sharp edge to reduce friction as they are driven through the tube walls and brim. Since the brim is compressed when placed in the delivery tube, the brim must be manufactured of pliable material that will return to its original shape after this deformation. The brim must be soft enough to allow puncture by the stiff sutures. Chemicals for stimulating growth and inhibiting infection are imbedded (at manufacture) in the core particularly around the junction between brim and stem. Chemicals to make the openings in walls slip over the brim in the desired direction may also be applied.

In applications where the graft core and graft are to remain in the body permanently, they are bonded together. They may be made of the same or different material at the factory. In any case, the hollow sutures are made of a harder inert material than the graft core, and the stiff sutures of an even stiffer material. An epoxy glue of the type that bonds when the A and B parts are mixed may be used to make a long-lasting bond between stiff sutures and the brim. Part A is in the brim and part B on the stiff sutures. The thin layers of A and B mix as the stiff sutures move through the brim. The stiff sutures must be of a material flexible enough to resist breaking from a plurality of heart beats if they are flexed for years of such beating.

FIG. 4 f shows push-rod balloon 31 and attached rods 32 used for pushing stiff sutures 27 through the edges of openings in natural tubes of the body and into the brim. The purpose of using use the push-rod balloon to drive the stiff sutures in the brim is to complete the suturing of the anastomosis from inside the body tubes rather than from outside the body tubes as is done in manual suturing. More details regarding the push-rod balloon and the graft core 12 will be shown later. A less preferred embodiment of the push-rod balloon is to utilize two, a distal and a proximal, with rods facing in only one direction. This alternative embodiment is sufficiently obvious as not to need an illustration. The advantage of combining rods in both directions is that one push-rod balloon need not be withdrawn for the other to be advanced. If there are application situations where the anastomosis with the first tube 1 is of much larger diameter than that with the second tube 2, one push-rod balloon 31 may not be capable of changing diameter to the extent necessary. Then distal and proximal push-rod balloons of different sizes would be required.

Twelve rods 32 are exposed in the distal and proximal directions so they can be used for pushing stiff sutures 27 in one direction and pulling against them in the other direction without having to remove the push-rod balloon from inside the delivery tube. Push-rod catheter 33 to which the push-rod balloon is attached is also shown. In the deflated state push-rod balloon 31 is advanced in the delivery tube catheter just proximal to the base of the distal graft core with rods 32 inside the stem of distal graft core 12. After several steps described later, push-rod balloon 31 is withdrawn from the stem and inflated. This inflation brings rods 32 in alignment with stiff sutures 27 inside the hollow sutures. Key 34 is shown attached to the distal end of push-rod catheter 33. This key is small but can be seen in this view. The function of the key is to align the rod with the proper stiff suture. This will be discussed again in the context of the figure which shows the matching keyway inside the stem of the graft core. When push-rod balloon 31 is advanced, rods 32 push stiff sutures 27 from the base of the core stem to the point where it turns at forty-five degrees (for instance) to emerge from the stem. This action moves the stiff sutures 27 from the end of the hollow sutures through tissue surrounding an open edge of the body tube and into the brim. The stiff sutures have barbs on their surface to keep them from retreating from the position to which they are advanced. These barbs become embedded in the brim and in the hollow sutures from the point where they turn to emerge from the stem. If the bond of stiff suture and brim is not strong enough a small amount of appropriate glue may be added at the place where the stiff suture enters the brim.

In like manner, the proximal rods are used to pull against the stiff sutures 27 in the proximal graft core 12 driving them through the first body tube and into the brim. This action with the push-rod balloon is performed when the brim is inside the lumen of a body tube.

Cutting devices are needed to exit the first tube (aorta) and enter the second tube (artery). There are a variety of conditions in which the tubes of the body exist, some being deviant from normal. Cutting devices of various types will be needed for this diversity of conditions. To accommodate this, five alternative embodiments of the invention provide five cutting devices. Each is designed for use in certain conditions that could be encountered in an application situation. The physician decides which to use after preoperative examination or (if necessary) during the operation. Variations on these five devices are obvious as is the use of chemicals on blade surfaces to inhibit bleeding.

FIG. 5 a shows circular excision device 35 in the inflated state. A relatively large diameter first tube is required to maneuver this device to a position of about ninety degrees with respect to the tube wall. The aorta is such a tube so this device is one the physician may choose for cutting the opening that allows devices to emerge from the aorta, enter the pericardium and travel to the coronary artery.

Circular microtome blade 36 is inside balloon 37 when deflated and rises out of the balloon when inflated to excise a disk of tissue when pushed forward. An advantage of cutting a round opening is that the endothelial layer is thereby equally exposed around the entire circumference. This is not the case with a slit. It is also not the case with devices that twist their way through the aorta wall unevenly throwing off bits of tissue.

A cruciform conical arrow 38 and its guide wire 39 are manipulated independently of balloon 37 and pass through a tunnel in the center of the balloon created by a catheter to which the balloon is attached and are thus advanced to the target site of anastomosis along with balloon 37. The clamping catheter is maneuvered to about ninety degrees with respect to the wall at the target site. The balloon is inflated causing the circular microtome blade 36 to extend from the distal end of the balloon as shown. The inflation also causes the balloon to push against the wall of clamping catheter 70, effectively joining to it by pressure.

Cruciform conical arrow 38 is pushed by its guide wire 39 out of the tunnel running through the balloon and through the wall of tube 1.

A serrated microtome blade 36 is pushed forward by its own catheter or by the clamping catheter to which it is joined by inflation pressure, to cut a disc of tissue from the body tube wall. Blade 36 has sufficient depth to cut entirely through (the expected) thickness of the first tube wall so there are no tissue connections holding the disc to the wall. The blade is serrated to engage cutting the tissue at an angle. The number of serrations is variable. The four shown are merely for example. The shape of the serrations is such that no twisting of the blade is needed. That is because in many applications, including those in the aorta, twisting the catheter on which the balloon is mounted would be likely to move said catheter away from its location. Radiopaque markers on the blade serrations show on the fluoroscopic equipment when the blade is through the wall.

At this point the clamping balloons on the clamping catheter clamp the opening to prevent blood from escaping into the pericardium. This clamping action is described later. But only after it occurs is conical arrow 38 withdrawn into the balloon tunnel. The blunt proximal side of conical arrow 38 keeps the disc of tissue on the arrow. The balloon is deflated. This returns the blade to a protected position inside balloon 37 and releases the balloon from the pressure connection with the clamping catheter. Balloon 37 and conical arrow 38 are withdrawn through the clamping catheter with the tissue disc spitted on guide wire 39.

FIG. 5 b shows a cylindrical slicing device 40 in two views, inside and outside a cylinder 41 that encases the mechanism. This device is used in situations where blade arm 42 must operate at (more or less) right angles to the axis of the catheter in which it is advanced and there are no body parts in the arc of the blade except the body tube being cut. Components and their mechanism of action are described.

Cylinder 41 encasing microtome blade arm 42 is of a diameter to fit snugly in the catheter through which it is advanced. Radiopaque marker 43 on the distal end of the cylinder is compared to a marker on the end of delivery tube 10 to advance the cylinder sufficiently to expose slot 48 in the cylinder through which blade arm 42 will travel, while leaving a sufficient portion of cylinder 41 inside the clamping catheter for support. The operator pulls back on the control (not shown and exterior to the mammalian body) which draws guide wire 44 back between two pulleys 45 embedded in the wall of the cylinder. This deploys blade arm 42 through its arc. The blade arm is attached at the proximal end to spring 46 whose other end is connected to support rod 47. Support rod 47 is embedded in the cylinder wall opposite slot 48 where the blade arm emerges when pulled. Once the cut is made the spring returns blade arm 42 inside cylinder 41.

FIG. 5 c shows device 43 being advanced forward of the delivery tube 10 to cut tube 2 with blade arm 42.

FIG. 5 d shows two views of a tracked slitter 49. This form of cutting device has the advantage of not needing to be deflated after cutting. It has the disadvantage of being complex with many moving parts. Tracked slitter 49 may be advanced into the lumen immediately because the blade is hidden at the end of the track. Components and their mechanism of action are shown and described. Exploded views are used because components would obscure each other if shown as they are actually placed.

Track 50 is shown here as a cylinder with a slot above, except at its end. Track 50 could be of a different shape. The important characteristic of the track is that it is slidably engaged with moving element 52 so the moving element will not wobble or twist as it is drawn through tunnel 51. Moving element 52 is shown at three locations along the track, beginning, middle and end and above the track so as not to obscure it from view. Moving element 52 has a slot in it to allow a swivel blade 53 to extend outside when it rises. The swivel blade is pivotally mounted on an axle 54 that turns in the body of moving element 52. The swivel blade's original position in the track is lying flat in the tunnel, blade up. When the blade is pulled by a guide wire 55 (not shown in its entirety as its path is obvious and it would obscure many components if shown) attached to a pin 56 extending from the side of the blade, the swivel blade rises to the erect position (center image). The blade is held there by a bar 57 across the moving element. Continued pull on guide wire 55 drags erect blade 53 along the length of the track.

The track can be any length. The blade may be any length. The blade cuts as it moves. When it is a little more than a blade's length from the end of the track, a lever 58, attached to the top of the track engages bar 57 and pushes it down. Bar 57 drops, and without it to hold the blade erect, blade 53 drops as well. The blade descends into the track tunnel, blade down. Pulling guide wire 55 leads to pulley 59. Pulling guide wire 55 turns back 180 degrees on a pulley 59. Guide wire 55 leads to a pulley 60 near the midpoint of the track (not visible in figure) where it turns ninety degrees on that pulley and exits at the midpoint of the track. Guide wire 55 then continues in the delivery tube and back to the operator. Continued pulling on this guide wire pulls the moving element through hinged bar 61 into receptacle 62 where cylinder 50 is covered. The hinged bar is spring-loaded and closes behind the moving element.

Pushing back on pulling guide wire 55 does not open the door or free the moving element from the receptacle. But a push on the guide wire 55 does release the latch that holds the two halves of the track together. This causes the track to unlock from its straight position and fold at the middle. A hinge 63 swings on its upper side so the two halves of the track fold against each other. Pulling on guide wire 55 now draws the folded track back through the delivery catheter. The folded track occupies only a small space and so can be withdrawn through a small opening. The tracked slitter may be removed with the holding balloon on which it is mounted or drawn through the center opening in the holding balloon.

FIG. 5 e shows a circular push-blade balloon 64. Unlike the circular excision device, it does not require a ninety degree approach to the wall it will cut. However it cannot be used at an angle much more acute than that. As with the circular excision device, it moves forward with the catheter behind it also moving forward. Therefore it appears to have little or no advantage over the circular excision device unless they are found with experience. However the device has an advantage in being simple with few moving parts. Circular push-blade balloon 64 may be used with the second tube, so long as the intended angle between graft and body tube is close to 90 degrees and the second tube is large enough that the blade does not endanger the side opposite the cut. This combination of conditions is unlikely in a coronary artery to aorta bypass. However experience may show some advantages for this device in coronary bypass or application in other situations.

Balloon 64 includes non-compliant body 65, and compliant extender 66 which exposes the microtome blade 67 when inflated. When the balloon is semi-deflated the blade folds into the extender 66 and the extender folds back into the body 65 of the balloon. When inflated the balloon grips the catheter by pressure and is advanced by pushing the catheter it grips.

FIG. 5 f shows tubular push-blade balloon 68 deflated and as it is normally mounted, on holding balloon 69.

FIG. 5 g shows tubular push-blade balloon 68 inflated to extend the blade. Balloon 68 is usable only when mounted on holding balloon 69. Holding balloon 69 is of the same shape and radius as the inside surface of the brim with which it is used. Holding balloon 69 has its own inflation lumen and guide wire (not shown). Tubular push-blade balloon 68 has the advantage of being simple, usable at acute angles, and potentially saving seconds in certain situations. Its potential disadvantage is when the second tube is small the blade may be pushed forward too far and cut into the other side before it is deflated. If used with a small second tube the push-blade balloon must be deflated immediately after cutting to protect the opposite wall of the second tube from injury caused by an exposed blade.

FIG. 5 h shows tubular push-blade balloon 68 deflated and folded, ready to be withdrawn through the center opening in the holding balloon. In most, if not all situations the tubular push-blade balloon will not be folded and withdrawn before the holding balloon is also folded and withdrawn. They may be withdrawn together.

Equipment common to PCI catheter labs, include fluoroscopic devices for viewing tissue, radiopaque markers and contrast emitted from catheters. The screens on fluoroscopes often show the target from different directions allowing the Interventionist to combine images in a mental three-dimensional view. These fluoroscopic devices help track and thread a guiding catheter through the branches of the femoral artery into the ascending aorta, and then position the catheter at a right angle with respect to the aortic wall where the opening will be cut, and into the pericardium and on to the targeted coronary artery. These fluoroscopic devices and other localizing equipment are appropriate for use in the present applications with the present suite of devices and methods.

FIG. 6 a shows the distal end of clamping catheter 70 with two rings of deflated clamping balloons 71 and 72. The clamping catheter serves two functions. First it provides the traditional function of a PCI guiding catheter. This is the first catheter threaded from the site of percutaneous entry to the aorta. Thereafter all devices are guided through this catheter. The second function is that of clamping the opening made in the aorta wall by a cutting device. This second function is the one discussed here. The clamping catheter 70 is made in sizes and shapes that duplicate those of guiding and diagnostic catheters and is advanced through a sheath using the same methods and skills as normally used in PCI procedures. The shapes have names such as Judkins, Amplatz, Arani, etc. These are designed for maneuvering in the femoral artery, aorta and coronary arteries. The preferred embodiment of the devices and methods of the invention disclosed here include such shapes for the clamping catheter as are in common use in PCI situations not necessarily all possible shapes that might be required in all application situations. The clamping catheter is chosen by the physician to be of the appropriate length, diameter and end shape for use in each particular application. Whatever shape and size is selected, the clamping catheter is advanced through a natural or percutaneous entry to the site of anastomosis in first tube.

The opening in the first tube (aorta) is cut to fit the circumference of the stem of the graft core, not the circumference of the larger clamping catheter. Therefore, pushing the clamping catheter through a smaller opening forces the wall to a larger circumference. The pressure created by this action produces an inhibiting effect on bleeding from the open edge of the opening. When the clamp is removed the wall will return to the original unstretched size of the opening made for the stem.

A double wall 73 with a divider 74 between the halves of the crescent-shaped conduit made by the double wall is shown. Conduits for carrying the liquid that inflates the clamping balloons must take up space either inside or outside the wall of a single wall catheter. That is, they cannot be coincident with the catheter wall unless the wall is doubled in some way.

Because of the need to inflate the balloons quickly, this non-tubular conduit is designed to carry a larger volume than would two tubes that increase the diameter of the clamping catheter as much as does the double wall. An additional volume of fluid flows in the “wings’ of the crescent. One half of this crescent-shaped conduit has an entry port to the distal balloon 71 and the other half an entry port to the proximal balloon 72. Neither port can be seen in this view. The end of the clamping catheter is open in this diagram in order to view what is inside.

FIG. 6 b shows the distal clamping balloon 71 and proximal balloon 72 in their inflated state. These balloons clamp the opening in the aorta wall after an opening has been cut. The size of the opening will be smaller than the circumference of the clamping catheter in order to fit the (smaller) stem of the proximal graft core that will later be lodged in the opening. The circular excision balloon is likely to be used as it creates an opening that does not have points like the ends of slits that are more prone to tearing when the opening is stretched. However other cutting devices could be used under particular conditions. The figures and words used here are consistent with a ninety degree approach to the wall. The circular excision device 35 or circular push-blade balloon 64 is inflated in the distal end of the clamping catheter so that advancing the catheter pushes the circular cutting blade through the wall of the aorta followed by the clamping catheter. Being larger than the opening the clamping catheter compresses the surface of the open cut. This pressure temporarily inhibits blood from flowing from the edges of the cut as well as through the opening until distal clamping balloon 71 can be inflated. The proximal clamping balloon 72 is inflated prior to cutting but distal balloon 71 must remain deflated in order to fit through the opening. After inflation, the wall of first tube 1 lies between the balloons. It, is not shown in order for both balloons to be seen.

Radiopaque markers 75 are on the balloons and on the distal end of clamping catheter 70 for use in determining the location of the balloons by fluoroscopic means. These provide a means of determining when the distal balloon is exterior to the wall and the proximal balloon interior to the wall.

FIG. 6 c shows a cross-sectional view of one inflated clamping balloon. This view shows how the clamping balloons are specially shaped so that they do not touch the opening directly but create a ring of pressure at some distance from the opening in the wall. Curved member 76 is made of compliant material while straight portions 77 may be made of non-compliant material. The compliant material bulges around the balloon's circumference to squeeze the wall in proportion to the amount of inflation pressure. The pressure is adjusted to achieve the minimum balloon pressure that will control bleeding from the open cut and loss of fluid from the lumen of first tube. Once this is achieved the clamping catheter is ready to perform its role as a guiding catheter for all devices advanced through it. The cutting device is withdrawn.

FIG. 6 d shows a cross-section of the deflated distal clamping balloon 71 in a semi-inflated state and a conceptual diagram of the cross section. The purpose of these diagrams is to show how the compliant 76 segment and non-compliant support sections 77 can be folded in the deflated state.

Support section 77 is made of non-compliant material that unfolds to position the compliant section at a circumference larger than that of the clamping catheter to which the con-compliant sections are attached. This is done so as not to clamp directly on the edge of the opening that has just been cut. It is important not to injure, distort, or collapse the newly exposed intimal layer surrounding the opening. Avoiding injury to this innermost growth layer of tissue optimizes growth into a live anastomosis when the graft is live or optimizes healing of the open edge if the graft is of artificial material. The non-compliant sections pressing on opposite sides of the wall a small distance away from the catheter provide clam ping without pressing directly on the open end of the tissue snugly surrounding the catheter. As pressure is increased in the balloon the support section unfolds in relatively straight surfaces between the fold lines while the compliant material of the interface section bulges out in proportion to the internal pressure. This provides the necessary control of the amount of clamping pressure being applied to the two sides of the wall of the first tube. The pressure must be sufficient-to stop bleeding and to seal the opening to prevent leakage of fluid from the first tube without inducing spasms.

FIG. 7 shows the distal end of an explorer guide wire 79. Finding the target area will be more difficult in some application situations than in others. Therefore several means of tracking the explorer guide wire to the desired site are provided.

Guide wire 79 has a J-tip bent by the physician to the curved shape wanted for the situation. The tip of guide wire 79 has screw threads 80 on it. This enables the physician to embed the screw threads in the second tube 2 when the target area is located. The distal end of the explorer guide wire also has an opaque marker 81 along its length. This allows it to be seen in orthogonal views of the fluoroscopic display. Thus its maneuvering can be seen in three dimensions. For situation where the physician needs more help in locating the desired site, a target guide wire 82 can be advanced to the target area through the narrowed area in the artery (second tube 2).

FIG. 8 shows target guide wire 82 in second tube 2, with its longitudinal opaque marker 83 lining up with marker 81 on the explorer guide wire tip. This alignment makes the longitudinal axes of the two tubes parallel as well as close as the physician observes in two orthogonal fluoroscopic views.

After alignment, the screw-threaded tip is twisted into the second tube at the target area. The delivery tube with cutting device mounted on the holding balloon is advanced immediately on the explorer guide wire to make the slit at the target. Thus the embedded tip does not have to remain in place for more than a few seconds, reducing the possibility that fluid can leak from the target site. Fluoroscopic devices are one of the faster growing fields, so orthogonal fluoroscopic images will be available in most well-equipped catheter laboratories. However other devices, such as the following can be used if adequate fluoroscopic images are not available.

FIG. 9 a shows the explorer guide wire 79 with its screw tip 80 as a transmitter and the target guide wire 82 with a receiver tip 84. Signal strength increases as the distance between transmitter and receiver decreases and the display would display this information to the physician to guide the transmitter and receiver until only the wall of the second tube separates them.

The radio frequency (RF) signal to the transmitter is sent through the metal wire of the explorer guide wire, thus requiring no added space. The connection from the receiver to a display may require two wires. In this case a dual guide wire would be used as there is adequate space for guide wires in the second tube.

FIG. 9 b shows the locations of the two transmitters 80 and 85, with a time delay line 86 between them. Also shown are receivers 84 and 87 with the time delay line 88 between them. The opaque markers 81 and 83 are in white rather than black, as used in previous figures.

Since it is important for the slit to be aligned precisely on the longitudinal axis of the second tube, two transmitters and receivers in line may be used. The same RF signal is used for the two transmitters and receivers but a time delay line is placed between the two so they are distinguishable in time. The circuit in the display is sensitive to the strength of signal between the transmitter-receiver pair that sends and receives at the same time. Thus when each pair is separated only by the wall of the second tube they are in longitudinal alignment as well as in immediate proximity.

FIG. 9 c shows south (S) and north (N) poles of electromagnet 101 in target guide wire 82. This is a magnetic alternative to two RF transmitters. The electromagnet may have sufficient strength to draw the cutting blade toward it and keep the blade in place even with a beating heart. To increase the strength of attraction the blade may be magnetized as a permanent magnet. Care must be taken to mark its poles so they are appropriately aligned opposite the N and S poles in explorer guide wire 79.

FIG. 9 d shows two transmitters 84 and 87 with delay line 86 between them mounted in the target guide wire 82 surrounded by four receivers 89, 90, 91 and 92 on the distal opening 93 of the delivery tube 10. This arrangement of transmitters and receivers is chosen for situations where the explorer guide wire does not provide sufficient accuracy for longitudinal alignment.

The four receivers are shown on the delivery tube as it, is advanced over the explorer guide wire to the target site. The receiver in the twelve o'clock position 89, is timed to receive the signal from the distal transmitter and the receiver in the 6 o'clock position 90, from the proximal transmitter. The receiver 91 in the 3 o'clock position and the receiver in the 6 o'clock position 92 are timed to receive first from one transmitter and then the other. The circuitry of receivers 91 and 92 compares the signal strength from each, transmitter to determine when they are equal. They are then equidistant longitudinally. This circuitry also compares signal strength from each side to determine when they are equal to assure lateral equidistance. This circuitry is a variation of the century-old arrangement known as Wheatstone's bridge. When all comparisons are balanced the four receivers will be accurately positioned outside the graft and in line with its longitudinal axis. This arrangement need be taken only when necessary in a difficult application situation. Physicians who specialize in different application situations will quickly determine which devices and methods are appropriate for them.

FIG. 10 a shows a holding balloon 69, with a cutting device embedded, that covers the opening in the distal end of delivery tube 10 as it follows along the explorer guide wire 79. The center opening in holding balloon 69 is for withdrawing the cutting device after use. It also provides the exit notch for explorer guide wire 79. When explorer guide wire 79 was initially advanced toward the target site from the site of the clamping balloon 72 it was through this center opening in holding balloon 69.

FIG. 10 b shows the push-blade balloon 68 inflated and ready to cut at the site where the explorer guide wire is screwed in the second tube. This is the situation after delivery tube 10 is advanced past the site of the clamping balloons over the explorer guide wire to where the explorer guide wire is screwed into the target. The delivery tube contains the graft with graft cores on each end.

When the end of the delivery tube is at the target site the holding balloon is against and conforming to the outside wall of the second tube. If the cutting device mounted on the holding balloon is a tubular push-blade balloon, it is inflated to expose the blade and the slit made by pushing it through the artery. If the cutting device is a tracked slitter no inflation is necessary, the wire controlling the blade is drawn, the slit is made and the blade sheathed. When a push-blade is used the balloon must be deflated to hide the blade before or as the delivery tube is advanced through the opening. Either cutting device may be withdrawn at this time or may be left in place as the delivery tube is advanced into the lumen of the second tube 2. Certain forms of cutting devices together with second tubes of small size create a danger to the wall opposite the opening if they are advanced without covering the blade by deflation. The cutting device and holding balloon are deflated and withdrawn outside the body after the anastomosis is completed. The length of the slit made is the length of the blade or the length of travel on the track. After the slit is made, the delivery tube is immediately advanced through the slit opening and pushed downstream in the lumen of the second tube until its heel is also in the lumen. Radiopaque markers on the heel and toe assist the physician in determining when the delivery tube's heel is inside the lumen.

As with all cutting devices the device size is determined by the diameter of the stem of the graft core. The length of the slit must be approximately one-half the circumference of the stem. This is because each side of the slit fits around one-half the stem. The stem axis is most likely to be at an angle, thus the circumference of the oval is greater than the circumference of an intersection at a 90 degree angle. The 90 degree angle circumference of the stem is about 3.14 (pi) times the outside diameter of the stem. Thus the correct length of the slit to be cut is approximately one-half of 3.14 times the stem diameter. Dividing 3.14 by 2 yields 1.57. The cutting device selected should cut a slit that is about 1.57 times the diameter of the stem for a 90 degree intersection between the graft and the artery. An additional length must be added as a function of the acuteness of the angle of intersection. This is just one of the approximate relationships among the dimensions of the devices.

A way of ensuring that the size relationships noted above and those described in a later paragraph are maintained is for the manufacturer to assemble a correctly sized set of all the devices of this suite. The physician selects the correct suite based on the diameters of the first and second tube that are to be joined and the thickness of the graft. The physician has a choice regarding cutting devices and-type of device for guiding the delivery tube. But once those sizes are determined prior to the operation, the sizing of the suite of devices is fixed and not a matter of preference unless the physician encounters unanticipated situations during the operation.

FIG. 10 c shows deflated push-rod balloon 31 near the base of graft core 12. The circumference of distal rods 32 lie in a smaller circumference than the circumference of hollow cones 28 on the base of stem 18. Only after the delivery tube has been removed can this view be seen. Before that, rods 32 were still inside stem 18. Push-rod balloon 31 was partially inflated, thus pressing rods 32 against the inside of stem 18 and expanding lip 94 of the balloon sufficiently to engage the base of stem 18 for pushing. At the same time the holding balloon was pulled against the brim to grip on the graft core as the delivery tube was withdrawn. When withdrawn, brim 19, no longer compressed, expanded inside the lumen of second tube 2 and the opening in the side of second tube 2 closed around the stem of the graft core. Deflating push-rod balloon 31 releases the pressure of distal rods 32 against the inside of stem 18 so push-rod balloon 31 can be withdrawn resulting in the condition seen in FIG. 10 c. Second tube 2 and graft 3 are not shown so this condition can be seen.

Keyway 95 is shown on the interior of stem 18. Key 34 is shown attached to the push-rod catheter. This key and keyway ensure that the push-rod balloon is oriented so the proper rods engage the stiff sutures for which they are intended.

Rods 32 are covered by a shaped cap so they do not catch on anything such as graft 3 attached to stem 18, especially as the push-rod balloon is withdrawn to the position shown.

Also not shown are stiff sutures 27 inside stem 18. However the proximal end of each stiff suture is located at a hollow cone 28. This is the case with the embodiment illustrated. In an alternative embodiment the stiff sutures may be placed at varying distances away from the hollow cones in the base by the distance that said stiff sutures travel a shorter distance than the stiff suture(s) that travel(s) the longest distance. In that embodiment the proximal rods would all be of the same length. In the illustrated embodiment, the rods 32 are shown with different lengths. The longest rod is for driving the stiff suture that travels the greatest distance to reach and enter the brim. The longest distance is at the point where the tangential angle is most obtuse, the 3 and 9 o'clock positions. Generally the more obtuse the tangential angle the longer the distance. The thickness of the graft is also a factor in this distance. Generally, the thicker the graft, the longer the distance. However these distances are computed by the manufacturer from tables given in a later paragraph. The differences in length shown are illustrative that there are differences and the ends of the rods form a pattern. The actual differences are computed as the distance of longest travel minus the difference of shortest travel. The longest rod touches its stiff suture(s) first and pushes it some distance before the second longest rods engage their stiff sutures, and so on. The longest rod has been driving its stiff suture(s) most of the distance to the brim when the shortest rod engages its stiff suture(s).

FIG. 10 d shows push-rod balloon 31 inflated, placing twelve rods 32, in the same circumference as the stiff sutures inside the hollow sutures inside the stem. The relationship of key 34, shown in position in FIG. 4 f and the keyway 95 shown in position in this figure as well as in detail are important in keeping the proper rods aligned with the stiff sutures they drive. The rods 32 are seen properly aligned with and ready to push stiff sutures 27 located within the hollow sutures in the stem of the graft core 12.

To complete the anastomosis the stiff sutures are driven by the push-rod balloon through the edge of the opening in the second tube and into the brim inside the lumen of the second tube. The holding balloon is continually drawn in the proximal direction to hold the brim against the wall of the second tube while the pressure from the rods driving the stiff sutures exert pressure in the distal direction. All stiff sutures are driven simultaneously to maintain balance around the circumference. To drive each separately would pull in the direction of each as it was driven. Another advantage of simultaneously driving the stiff sutures is that it requires only seconds to accomplish. Thus the conditions for a good graft are met and the stiff sutures are driven through the wall of the second tube and into the brim now inside the lumen of the graft. This completes the anastomosis of the second tube and now the anastomosis with the first tube must be made.

Holding balloon 69 and the cutting device are deflated and removed. The push-rod balloon is deflated so the rods are protected from jabbing the graft as they are drawn back through the graft in the delivery tube to the proximal graft core. The proximal rods are placed inside the graft core stem for stability as the delivery tube is removed. The key and keyway are lined up to accomplish this, thus ensuring that the proper rods and stiff sutures are aligned.

A holding balloon of the same shape as holding balloon 69 is advanced on a thick guide wire to hold the brim of the proximal graft core in place while the delivery tube is withdrawn. With the delivery tube withdrawn, the graft core brim expands inside the clamping catheter that is clamping the first tube (aorta). The brim is less compressed than it was in the delivery tube but it is of sufficient circumference to make a seal against the wall of the clamping catheter. The clamping balloons are deflated and the clamping catheter withdrawn a short distance. The brim expands and is pushed against the wall of the aorta by fluid pressure inside the aorta. The aorta wall closes around the stem extending through the opening. This forms a temporary seal and blood starts flowing toward the artery but not with full pressure as the push-rod balloon is still inside the graft producing resistance to flow. The same push-rod balloon is used, but with the proximal rods pushing the stiff sutures. Key 34 is set in keyway 95 of the proximal graft core so the rods engage the proper stiff sutures when the push-rod balloon is inflated. With the rods aligned with the stiff sutures the rods drive them through the edge of the opening in the aorta and into the brim being held in place by the proximal holding balloon. Radiopaque markers help the physician visualize positions of components. The clamping catheter is returned to the opening to receive the deflated push-rod balloon and deflated holding balloon. Once the push-rod balloon is inside the clamping catheter, the catheter is withdrawn. This completes the second anastomosis. Second and third bypasses may be conducted if required. After the last bypass is installed, the operation is finished with the conventional PCI closing procedures.

FIG. 11 a shows graft core 12 with graft 3 sutured on it (as was shown in FIG. 4 c with the addition of a cross section of the wall of the second tube and the stiff suture pushed through said wall and into the brim. Hollow sutures 25 and posts 26 are shown holding the graft to stem 18. Now stiff sutures 27 are also shown cutting through the wall of second tube 2 shown here in cross section. The wall of the tube 2 surrounds the stem along the junction and the angle of the wall approximates the miter as shown. That is, the wall's exterior layer pulls back more than the inner intimal layer after a slit is made along the longitudinal axis of the wall except at the 6 and 12 o'clock positions where the pull back is slight. However the pull back of the outer layer generally makes the inner layer closer to the junction creating a bevel of variable acuteness.

FIG. 11 b shows the same elements as FIG. 11 a but at the 3 and 9 o'clock positions and with the inside surface of the tube also shown. If the outside surface were shown it would obscure the cross-sectional segment of the tube wall. The ghost of the brim is shown inside the tube. The stiff sutures are shown as having gone through the wall and lodged in the brim inside the lumen.

It is evident that there are relationships among the various devices of the present invention, particularly with respect to size. There are also infinities of possible angles and dimensions. One of the ways of dealing with infinities of variables is that used with PCI devices such as catheters. Catheters are sized in production according to the French system. One French unit is one-third of a millimeter, three French units are one millimeter, nine French is three millimeters and so on. The units are normally abbreviated as 1F, 2F, etc. This refers to inside diameters. The advantages of following the already established French convention are obvious but this in no way limits the dimensions of the present invention to French sizes. In addition there are relationships among the sizes of devices in the suite as described in this application for patent. The sizes vary with application situation but the relationships of sizes remain fairly constant. Using these relationships, as with using the French system of sizing reduces an infinity of possibilities to a meaningful manageable number. Without limiting the present invention to any particular sizes or relationships, the sizes and relationships in Table 1 offer a practical way of managing an infinity of possibilities.

Table 1 gives typical sizes of the first tube and thickness of graft in coronary artery bypass application situations. These sizes would be determined prior to the operation and be used to select the proper size graft core and supporting suite of devices. In addition the physician would also determine the length of graft between the sites selected for anastomosis. The method the physician uses to make the measurements will affect the results. For instance, a measurement made inside the lumen of the coronary artery will give a different result than a measurement made exterior to the same coronary artery at the same site. By either measurement the thickness of the coronary artery wall would have to be estimated to provide an estimate of the other dimension. Such estimating is expected and device sizes are sufficiently fungible to tolerate estimates. Likewise the relationships of device sizes are more rules-of-thumb than precise formulas. It is in this way that the values are given in Table 1. These, like the French system, give particular sizes, eliminating all in between. They also use particular (approximate) sizes of devices that all have appropriate dimensions for small body tubes. The relationships among the sizes as well as the sizes may be extrapolated to larger sizes. A column of figures in Table 1 represents the approximate sizes to be used together as a suite for one application. A new column of figures can be created by extrapolating from the numbers given in Table 1. TABLE 1 Tube OD 3.6 3.0 2.4 2.1 1.5 Brim OD 2.8 2.4 2.1 1.5 1.2 Brim ID 2.1 1.8 1.5 1.2 0.9 Stem OD 2.1 1.8 1.5 1.2 0.9 Stem Thick 0.3 0.3 0.15 0.15 0.15 Hollow Sut 0.15 0.125 0.1 0.07 0.05 Stiff Suture 0.07 0.05 0.05 0.035 0.025

In Table 1 all entries are in millimeters. The Tube OD is the outside diameter of the smaller tube (usually the second tube) to be joined. Stem thickness is abbreviated Stem Thick and suture as Sut. The preferred embodiment of the present invention includes reasonable consistency in the relationships of sizes of the device in the suite.

Relationships regarding tangential angles, thickness of grafts and distance stiff sutures must travel are dealt with in the following figures.

FIG. 12 a shows a graft core where the longitudinal axes of stem and brim intersect at 45 degrees, producing an angle of intersection 21 of 45 degrees at the 6 o'clock position and 135 degrees at the 12 o'clock position. A plane 96 at right angles to the tangent at surface of said stem has been erected at the 12 o'clock position. This shows tangential angle 97 of stem and brim at this position and it is the same as the angle of intersection at this position. It is also the same at the 6 o'clock position. But the angles of intersection are different at all other points on the junction.

FIG. 12 b shows the graft core rotated to the 2 o'clock position and plane 96 erected at a right angle to the tangent at that point on the junction to show tangential angle 97 of about 152 degrees at the 2 o'clock position. Half this angle is about 76 degrees for entry in the groove of cutting sleeve. It is larger than the tangential angle at 12 o'clock.

FIG. 12 c shows the tangential angle 97 at the 3 o'clock position. It is about 167 degrees and still more obtuse. It is evident that the greater the tangential angle the longer the distance the sutures must travel to reach the brim. However the distance is also a function of the thickness of the graft.

FIG. 12 d shows a cross section of two grafts 98 and 99 on the same stem. This is for purposes of comparison as two grafts are never so placed in an application. Miter angle 100 is shown. Two hollow sutures and two stiff sutures are shown schematically because numbers on them would obscure their location. Each hollow suture comes out of the stem at 45 degrees toward the point of intersection of the miter flange and their graft. It is evident that the thicker the graft the farther the distance the stiff suture must travel to reach the brim. Without calculating all the possible distances, it is evident that they can be calculated. It is also evident that, like the French system for catheters, some conventions must be used to limit sizes from the infinite number of possibilities.

Conclusions, Ramifications, Scope

Thus the reader will see that I have provided the devices and methods for accomplishing better anastomoses, faster and with better growth potential than possible with any form of prior art and most importantly while avoiding the severe collateral damage characteristic of prior art that required intensive care in hospital and long, painful recovery thereafter. Specifically, the products are fluid-tight anastomoses of natural or artificial bypass grafts to body tubes by combination suture and seal devices. Sizing and shaping of the graft for optimal growth and most suturing is completed before the operation starts and finished from inside the graft to body tubes being connected in seconds. The graft and graft cores devices are delivered without injury to the site of anastomoses intraluminally after percutaneous or natural entry to the body. Special devices for tracking and for aligning micro cutting blades to sites for optimal openings of body tubes are provided as well as a clamping device to prevent leakage after openings are cut.

Although the present invention has been described with reference to preferred embodiments, workers skilled in the art will recognize that changes may be made in form and detail without departing from the spirit and scope of the invention. Thus the scope of the invention should be determined by the appended claims and their legal equivalents, rather than by the examples given. 

1-52. (canceled)
 53. A graft core device for drawing together two body tubes in an animal to make an end-to-side anastomosis, comprising, a. a stem section having a tubular shape and a wall with inner and outer circumferences, a circular planar base end, and an opposite end, b. a brim section having a tubular shape and a wall having inner and outer circumferences, c. said brim section attached to said stem section at a junction so that said sections form an angle from 30 to 90 degrees, d. said brim section having a central opening, e. said brim section being made of material flexible enough to be compressed to a circumference slightly larger than the outer circumference of said stem section, but having sufficient shape memory to return to its original shape upon removal from compression, f. said stem section being made of relatively inflexible material having a plurality of segments of different types of suture material embedded in, and fastened to said stem section, g. a plurality of hollow suture segments having a tubular shape, made of relatively stiff, hard material, and longitudinally embedded in said wall of said stem section, starting close to said circular planar base end and proceeding longitudinally in said wall, emerging radially from said wall at an angle with respect to said stem section's longitudinal axis, and extending out from said wall and with ends pointed toward said brim section, h. a plurality of post segments of stretch-resistant suture material capable of returning to their original shape after bending, i. said plurality of post segments extending from near said junction of said brim and stem sections, radially aligned with, pointed in the direction of, and of a length to intersect said ends of said plurality of hollow suture segments, j. said plurality of post segments further including means for forming respective connections to said plurality of hollow suture segments, thus creating a first plurality of closeable loops, each consisting of said post segment attached to said hollow suture segment and said wall of said stem section being the third side, k. a plurality of stiff suture segments constructed of stiff but bendable suture material, l. said stiff suture segments being slidably located inside said respective hollow suture segments but capable of being pushed out of said hollow suture segments, and m. said stiff sutures being sufficiently sharp to drive through body tissue and into said brim section, thus creating a second plurality of closable loops, each consisting of said stiff suture segment, said post segment, and said wall of said brim section being the third side, whereby (a) said stem section can be attached to an end of a first body tube by said first plurality of loops, (b) said brim section, while compressed, can be inserted in an opening made in the side of a second body tube and (c) when uncompressed expanding inside said second body tube to form a seal between said first and said second body tubes and (d) when attached to said wall of said second body tube by said second plurality of loops, (e) thereby holding said two body tubes in such contact as to create a more fluid-tight end-to-side anastomosis at said junction of said stem and brim sections of said graft core device than can a seal alone or sutures alone.
 54. The device of claim 53, further including: a. a plurality of female rings on the respective ends of said plurality of post segments, each female ring having an annular female groove inside so that each ring can snap together with a male annular ring on the end of one of said plurality of hollow suture segments, thus providing a means of connecting said post segments and said hollow suture segments, b. a plurality of circular suture segments, constructed of stretch-resistant suture material and connected to said post segments so as to create a circumference of suture segments, said circular suture segments being attached or capable of being attached to said post segments where said post segments connect to said hollow suture segments, thus creating resistance to any force exerted to increase the circumference of said circular suture, including back pressure from said hollow suture segments connected to said post segments, c. a plurality of flaps or barbs on said plurality of stiff suture segments that fold flat against said stiff suture segments while being pushed out of said hollow suture segments but deploy outward when said stiff suture segments tend to move back into said hollow suture segments, thus preventing said stiff suture segments from backing into said hollow suture segments after being driven into said brim section and drawing said brim section into closer contact with said lumen of said body tube for a tighter seal between said brim section and said lumen of said body tube than exists before said flaps or barbs are embedded in said brim section, d. said plurality of hollow suture segments each having an end of conical or hemispheric shape and located in the base of said stem section where said plurality of hollow suture segments start, thus forming indents in said base capable of guiding a plurality of rod from another device into alignment with said stiff suture inside said hollow suture, and e. a shallow longitudinal groove on the interior of said stem section that acts as a keyway, allowing a protrusion on another device to enter as a key, thus aligning said stem section with said other device in a predetermined desired orientation.
 55. The device of claim 53 wherein said graft core device is manufactured of a biodegradable material that will be absorbed by the body after said graft tube, from the patient's body or from the body of a compatible donor, has grown together with said body tube, said graft core device being coated with a pharmaceutical composition for promoting growth between said graft tube and said body tube.
 56. The device of claim 53 wherein said graft core device is made of biocompatible, non-biodegradable material that is joined to said graft tube, said graft tube being made of similar artificial biocompatible material such that said graft core device and said graft tube, being of non-biodegradable material, remain in the body permanently as a combination graft tube and graft core device that will not grow together with said first and second body tubes and will provide the support functions of said post segments and said circular suture segments of said graft core device so that the only suture components attached or imbedded in said graft core of non-biodegradable material are said hollow suture segments and said stiff sutures segments that also are made of biocompatible, non-biodegradable material.
 57. The device of claim 53 wherein said brim section of said graft core device extends outward from the outside of said stem section by a distance that is a function of the thickness of a wall of said graft tube and the tangential angle at which said brim section and said stem section meet at the points and where said posts emerge from said junction of said brim section and said stem section, said brim section having a plurality of small indents and ridges near the points where said stiff sutures enter said brim section, thus preventing said stiff sutures from skidding along the outer surface of said brim when being pushed into said brim.
 58. The device of claim 53 wherein a. a first plurality of said stiff suture segments have sharp conical points, b. a second plurality of said stiff suture segments have been made sharp by truncating said stiff suture segments at an angle to their longitudinal axis, thus creating a means of affecting the direction of travel of said stiff suture segments toward the cutting edge and away from the flat face, and c. said flat face on said second plurality of stiff suture segments are placed in said hollow suture segments so as to drive said stiff suture segments toward said brim section.
 59. The device of claim 53 wherein each of said plurality of stiff suture segments is positioned in each of said plurality of hollow suture segments at a predetermined distance from each of said ends of said each of said plurality of hollow suture segments, the distance for each being based on a computation of the distance each stiff suture must travel from the end of said hollow suture to a target location on said brim.
 60. The device of claim 53 wherein said stiff sutures are positioned in said plurality of hollow suture segments at said ends of said plurality of hollow suture segments.
 61. The device of claim 53 wherein the outer surface of said brim section has a coating of a slippery substance for moving the inner layer of said body tube easily over said outer surface so said inner layer of said body tube does not stick to said outer surface and curl thereunder.
 62. The device of claim 53 further including mussel or biocompatible glue requiring the mixture of two parts for activation, one part being on said target of said each of said plurality of stiff suture segments on said brim section and the other part being on the end of said stiff suture segment.
 63. A push-rod balloon device for pushing a graft core device and a plurality of stiff sutures of said graft core device, comprising: a. a cylindrical balloon segment in the general shape of a cylinder with closed ends, b. a push-rod catheter attached to said cylindrical balloon segment, c. the distal end of said push-rod catheter forming a non-collapsing tunnel through the longitudinal axis of said cylindrical balloon segment, d. said push-rod catheter being sufficiently stiff to resist kinking when force is applied to push the adjacent graft core device and said plurality of stiff sutures of said graft core device, e. a plurality of parallel rods extending through and beyond said closed ends of said cylindrical balloon segment, f. said plurality of parallel rods arranged in a ring around said push-rod catheter, g. said cylindrical balloon segment made of balloon materials differentially compliant to fluid pressure produced inside said cylindrical balloon segment so as to cause said cylindrical balloon segment to assume a predetermined shape in response to a predetermined amount of pressure, h. said cylindrical balloon segment, when in a deflated state, having an outside circumference slidingly smaller than the predetermined inside circumference of an adjacent stem section of said graft core device, i. said cylindrical balloon segment, when in a fully inflated state, being sized to cause said ring of said parallel rods to lie in a circumference equal to the predetermined circumference of the plurality of hollow sutures in the base of said adjacent stem section of said graft core device, j. said cylindrical balloon segment, when in said semi-inflated state, being sized to cause said plurality of parallel rods to lie in a ring with a circumference less than the predetermined inside circumference of said adjacent stem section of said graft core device, thus allowing said plurality of rods to slide inside said inside circumference of said adjacent stem section of said graft core device, k. said cylindrical balloon segment, in the semi-inflated state, being of a greater circumference than the predetermined inside circumference of said base of said adjacent stem section of said graft core device, thus creating a lip capable of resting against said base of said adjacent stem section of said graft core device, l. said cylindrical balloon segment being made of material sufficiently thick and so placed as to resist deformations around said plurality of rods due to back pressure as said rods drive said plurality of stiff sutures through a plurality of hollow sutures, through tissue in a second body tube and into said brim section of said graft core device, m. said plurality of parallel rods, equal in number and disposition to the number and disposition of said hollow and stiff sutures, n. said plurality of parallel rods each having a diameter so that when each enters one of said hollow sutures, it will push said stiff suture forward and be withdrawn from said hollow suture without creating a vacuum, o. said plurality of rods being of sufficient stiffness as not to buckle or bend significantly when applying sufficient force to said plurality of parallel rods to drive said plurality of stiff sutures through a plurality of hollow sutures, through tissue in a body tube, and into said brim section of said graft core device, p. a tube located within said push-rod catheter and attached to said cylindrical balloon segment for inflating and deflating said cylindrical balloon segment, and q. a protuberance or key on said push-rod catheter which passes through a keyway in said stem section of said graft core device but which prevents said push-rod catheter from entering said stem section in any other alignment than that of each of said rods with said stiff sutures said rod is intended to drive, whereby (a) said push-rod balloon device will push said graft core device out of said delivery tube device, (b) said brim section being released from compression expands to normal shape inside said body tube, (c) thereby sealing the opening in said body tube, (d) said parallel rods of said push-rod balloon will simultaneously push said plurality of stiff sutures from said hollow sutures, through said tissue and into said brim section of said graft core device thus finishing the suturing of the graft core device to said body tube, (e) thereby connecting said graft tube to said body tube by a combination of seal and suture more fluid tight than either seal or suture alone, and (f) the anastomosis being accomplished quickly, without the use of needles, without stopping the heart, without injuring said body tube or said graft tube or causing collateral damage to other body parts.
 64. The push-rod balloon device of claim 63 wherein said rods extend beyond said cylindrical balloon in both distal and proximal directions, and further including a plurality of protective covers for the ends of said rods.
 65. The push-rod balloon device of claim 63 wherein said rods extend beyond said cylindrical balloon in the distal direction only.
 66. The push-rod balloon device of claim 63 wherein said rods extend beyond said cylindrical balloon in the proximal direction only.
 67. The push-rod balloon device of claim 63 wherein the length of each of said rods is approximately equal to the distance each said stiff suture segment that each said rod is assigned to push must travel from the end of said hollow suture segment in which each said stiff suture segment is located to the brim section of said graft core device where each said stiff suture segment becomes imbedded, and all said stiff suture segments are approximately aligned with said base of said graft core device.
 68. The push-rod balloon device of claim 63 wherein the length of all said rods in said push-rod balloon device are the same and each said stiff suture segment is located in each said hollow suture segment at a distance from said base of said graft core device that is approximately equal to the distance each said stiff suture segment must travel from the end of said hollow suture segment in which each said stiff suture segment is located to the brim section of said graft core device where each said stiff suture segment becomes imbedded.
 69. A bench device for assisting a user to prepare a graft tube to fit a preselected anastomosis location connecting a first body tube to a second body tube, and attach each end of said graft tube to a stem section of a pair of graft core devices, each having a stem section of a predetermined circumference and a brim section of a predetermined curvature, such that said brim and stem sections form an angle and a junction therebetween, comprising: a. a pair of cutting sleeves, each having a tubular shape, a circumference equal to said preselected circumference of said stem section of each of said pair of graft core devices, and one tapered end, b. a groove in each of said pair of cutting sleeves, each groove having the shape of one of said junctions of said brim and said stem sections of one of said pair of graft core devices, and c. said groove in each of said pair of cutting sleeve having an angle of inclination with respect to the surface of said cutting sleeve equal to about one-half of said angle between said brim and stem sections of each of said pair of graft core devices, whereby said ends of said graft tube may be cut to the shape of said junctions of said pair of graft core devices with an angle of inclination half that of the angle between said ends of said graft tube at said locations of anastomosis on said first and second body tubes, thus forming a connection that is both fluid tight and growth conducing at said sites of anastomosis.
 70. The bench device of claim 69, further including a bench and a pair of support arms to aid a user in cutting said graft tube with said graft core devices mounted on said support arms, wherein: a. said bench is formed of a rigid material and has a top surface for mounting a plurality of components thereon, b. said pair of support arms each having an “L” shape, mounted near a respective opposite end of said bench, having an arm segment pointed toward the other support arm, and a leg segment attached to said bench, and c. said arm segment of each of said pair of support arms sized to allow mounting one of said pair of graft core devices of a predetermined size or one of a pair of cutting sleeve components of predetermined size on said bench device thereon.
 71. The bench device of claim 69 wherein said bench contains a slot, one of said pair of support arms being slidably mounted in said slot, said bench containing measurement marks to aid a user in cutting a length of graft tube to a predetermined length such as to fit between said preselected sites of anastomosis on said first and second body tubes, each of said measuring marks showing the distance between one end of said graft tube and said each of said measuring marks, whereby said one of said pair of support arms is set next to said one of said measuring marks that matches the predetermined distance between said anastomosis locations on said first and second body tubes.
 72. The bench device of claim 69 wherein each of said cutting sleeves has a plurality of tunnels in ending in a corresponding plurality of holes in the surface of said cutting sleeve, and further including: (a) a plurality of hypodermic needles equal in number to and being extensible from said support arms through said respective holes in said cutting sleeve, and (b) a lever for simultaneously pushing said hypodermic needles through said holes in said cutting sleeve and through said graft tube mounted around said cutting sleeve, whereby said ends of said graft tube are pierced for easy entry of a plurality of hollow sutures on each of said pair of graft core devices in preparation for suturing said ends of said graft tube to said pair of graft core devices.
 73. The bench device of claim 69, further including (a) a vacuum pump attached to said hypodermic needles for enabling a user to draw the tissue of said graft tube against the cutting edges of said hypodermic needles and wherein (b) said hypodermic needles are coated with or contain a sterile dye substance that colors the tissue of said graft tube to mark the locations on said graft tube where said hollow sutures are to be threaded through the holes made by said hypodermic needles.
 74. The bench device of claim 69, further including: a. a snapper for assisting a user in connecting the post segments of said graft core device and said hollow sutures of said graft core device, said snapper having a pair of springing arms with ends shaped to fit said post segments and said hollow sutures of said graft core device, b. a pair of compression tweezers, each having springing arms with ends shaped to fit around each of said brim sections of each of said graft core device to aid a user in compressing each of said brim sections while each of said pair of graft core devices is placed in said delivery tube segment, and c. a delivery tube rest having a U-shaped cross section extended between said support arms, for holding said delivery tube segment of said delivery tube device, whereby (a) said plurality of hollow suture segments being connected to a respective plurality of post segments of said pair of graft core devices completes the suturing of said ends of said graft tube to said stem sections of said pair of graft core devices under conditions more conducive to fluid tight connections than permitted by conditions within a body after said body has been entered, (b) a user is able to complete half the suturing before the operation starts to reduce the time to complete an anastomosis in the body, (c) said brim sections of said pair of graft core devices will be compressed so as to fit within a preselected circumference of a delivery tube segment of a delivery tube device, and (d) said pair of graft core devices are placed at opposite ends of said delivery tube segment, with said graft tube therebetween to provide a safe way of delivering said graft tube to said anastomosis sites safely and without inversion, reversion, or injury of any kind to said graft tube.
 75. A delivery tube device for facilitating an anastomosis of first and second body tubes, said delivery tube device comprising: a. a pair of graft core devices, each of said graft core devices having a stem section with two ends and a brim section, said stem and brim sections having a junction therebetween, b. a graft tube having two ends and a preselected length and circumference, one end of each of said stem sections being sutured to an end of a respective graft tube, and c. a delivery tube segment and a delivery catheter segment, said brim sections compressed within said delivery tube segment so that a delivery catheter can push said delivery tube segment to said anastomosis site, d. said delivery tube segment and said delivery catheter segment each having distal and proximal ends and substantially similar cylindrical shapes, enabling a fluid-tight connection between said segments, end to end, e. said distal end of said delivery catheter segment being shaped so that it can be attached to said proximal end of said delivery tube segment, end-to-end, f. said delivery tube segment having a length approximately equal to said preselected length of said graft tube, and g. said delivery tube segment having an inside circumference slightly greater than said preselected circumference of said ends of said graft tube, whereby said graft tube is safely protected by said delivery tube device during delivery from point of entry into the body to said preselected sites of anastomosis and said brim sections of said graft core devices are compressed to slightly more than the circumference of said ends of said graft tube.
 76. The delivery tube device of claim 75, further including: a. a distal holding balloon device, said distal holding balloon device being capable of being held in a distal end of said delivery tube device in a semi-inflated state and capable of being fully-inflated when removed from said distal end of said delivery tube device; b. said distal holding balloon device having a distal holding balloon segment that has the shape of said brim section of said graft core device in the inflated state, but with a smaller tunnel through the center, c. a holding balloon catheter permanently attached to said distal holding balloon segment, in such a manner as to form a non-collapsing tunnel through the center of said distal holding balloon segment, d. said distal holding balloon catheter attached to said distal holding balloon segment for pulling and maneuvering said distal holding balloon segment when removed from said delivery tube device and fully-inflated e. said distal holding balloon catheter having an inside circumference sufficiently large to contain a plurality of said guide wires and tubes for inflation and deflation, f. said distal holding balloon catheter being sufficiently resistant to kinking to maneuver and push said distal holding balloon segment, g. said distal holding balloon segment having a plurality of mounting fingers extending from its distal surface for providing a means of firmly attaching a cutting device to said distal surface of said distal holding balloon segment, h. said distal holding balloon segment, when in the fully inflated state, being of the approximate outer circumference of said brim section of said graft core device, i. said distal holding balloon segment, when in the semi-inflated state, having an outside circumference capable of fitting tightly inside said delivery tube device so as to create a temporary pressure connection, j. said distal holding balloon segment, when in the deflated state, having an outer circumference slightly greater than said distal holding balloon catheter, and k. a tube attached to said distal holding balloon segment for inflation and deflation, whereby (a) said pair of graft tube devices, being sutured to said ends of said graft tube pair of graft core devices, are protected during delivery, (b) no eversion or reversion of said graft tube or exposure to other sources of injury is required, (c) said cutting device is in a position to cut an opening in said second body tube, and (d) said distal holding balloon segment is in position to enter said opening, thus forming a temporary plug in said opening until said distal, holding balloon and said brim section of said graft core device, when in the distal location, can be pushed out of said delivery tube device to form part of a permanent anastomosis between said graft tube and said second body tube and support an expanded brim section of said graft core device against force from the opposite direction.
 77. The delivery tube device of claim 75, further including a plurality of radiopaque markers, visible on external fluoroscopic screens, attached to said delivery tube segment, so as to show the location of components devices carried inside said delivery tube segment.
 78. The delivery tube device of claim 75, further including a plurality of receivers of radio frequency energy mounted on said distal end of said delivery tube segment of said delivery tube device and further including circuitry for connecting said radio frequency receivers to a remote display.
 79. The delivery tube device of claim 75 wherein: a. said distal holding balloon has at least one annular protruding ring on its circumference when said distal holding balloon is in the semi-inflated state, b. said delivery tube device has at least one grooved annular ring on its inside circumference, each grooved annular ring having the same shape as said protruding annular ring on said distal balloon holding segment when said distal holding balloon segment is in the semi-inflated state, and c. said annular protruding rings are placed to mate with said annular grooved rings for a tighter connection than provided by pressure alone.
 80. The delivery tube device of claim 75 wherein said distal end of said delivery tube segment of said delivery tube device has a shape similar to that of said junction of said brim section and said stem section of said graft core device.
 81. A pushing balloon device for applying forward pressure against a graft core device, said graft core device having a stem section and a brim section, with said brim section being compressed to fit within a predetermined circumference of a proximal end of a delivery tube segment of a delivery tube device, comprising: a. a pushing balloon, which, when in the fully inflated state, has a shape that is generally in the shape of said brim section of said graft core device, b. said pushing balloon, when in the semi-inflated state, having the general shape of said brim section of said graft core device, but with an outside circumference about equal to said predetermined circumference of a proximal end of a delivery tube segment in which said brim section is in compression, c. a tube for carrying a liquid for inflation and deflation, said tube being attached to said pushing balloon, d. a heavy guide wire attached to said pushing balloon in such a manner as to push the circumference of said pushing balloon of said pushing balloon device against said brim section of said graft core device, and e. said heavy guide wire being of sufficient rigidity to resist kinking against force applied to said pushing balloon from the opposite direction, whereby (a) said semi-inflated pushing balloon device can apply pressure to said brim section compressed within said delivery tube device, thus holding said brim section in place while said delivery tube device is withdrawn, and (b) in the fully inflated state being of a size and shape to apply pressure over the surface of said brim section after said brim section is released from compression.
 82. A clamping catheter device for providing a closed pathway from a point of entry of a body to an opening cut in a first body tube at the site for an anastomosis, providing a pair of annular balloons for clamping said opening and thus providing a clamped portal to the second body tube, comprising: a. a double-wall catheter segment having a tubular shape sufficiently long to extend from said entry point in the body to a preselected said site of anastomosis on said first body tube, b. a double-wall conduit on one side of said double-wall catheter segment, said double-wall conduit being shaped as a crescent partitioned by a longitudinal divider, each side of said double-wall conduit having a lumen for delivering a high volume of liquid through a port leading to one of said pair of annular balloons, c. said double-wall catheter segment having an approximately circular interior cross-section such that a plurality of catheters and devices of essentially circular cross-section can slidably pass through or exert circumferential pressure equally around the interior surface of said double-wall catheter segment, d. said pair of annular balloons attached around a distal end of said double-wall clamping catheter in two approximately parallel planes at right angles to said double-wall clamping catheter, e. said two annular balloons being formed of a material differentially compliant to fluid pressure produced inside said annular balloon segments for causing said annular balloon segments to assume a predetermined shape in response to a predetermined amount of pressure, f. said annular balloons, when in the deflated state, being essentially flat against said guiding catheter segment attached to said annular balloons, g. said two annular balloons, when fully inflated, being in the general shape of an annular ring with bulging rim at their outer circumferences, h. each bulging rim being extended toward the other said bulging rim and sufficiently close to each other as to create a ring of pressure on tissue therebetween, i. each bulging rim being spaced around said opening such that the cut edge of tissue around said opening is not directly touched by said ring of pressure, and j. each bulging rim being positioned and shaped so that when said two annular balloons are over inflated, said ring of pressure will increase so that the flow of blood toward the edge of said opening will be blocked to prevent fluid from escaping said first body tube, whereby (a) a protective passageway from said point of entry to said first body tube is provided for advancing devices and catheters thus avoiding all collateral damage caused by entry through the chest, (b) clamping of an opening in said first body tube is provided that does not injure the intimal layer of tissue immediately surrounding said opening, (c) said double wall catheter provides large lumens that quickly inflate said annular balloons to prevent the escape of blood from said first body tube as said opening is cut, and (c) a safe portal to a second body tube is provided.
 83. The clamping catheter device of claim 82 wherein said double wall catheter segment is made of material sufficiently stiff and resistant to kinking to support some of the force required to push said circular cutting balloon device through said wall of said first body tube.
 84. A circular excision balloon device for excising a predetermined size disc of tissue from a wall of a first body tube and, with a dart on a guide wire, withdrawing said disc of tissue from the body through an excision catheter segment, the excised opening in said wall providing a portal to a second body tube and for anastomotizing an end of a graft tube device to said first body tube at approximately a 90-degree angle, comprising: a. an excision balloon segment having a cylindrical shape and a pair of closed ends, b. said balloon segment having a longitudinal axis and an interior pressure so that said closed ends bulge slightly, said closed ends generally intersecting said longitudinal axis at about ninety degrees, c. an excision catheter segment, said excision balloon segment being attached to a distal end of said excision catheter segment such that said excision catheter segment provides a non-collapsing tunnel through said longitudinal axis of said excision balloon segment, d. said excision catheter segment having the shape of a tube with a distal end attached to said excision balloon segment through said longitudinal axis of said excision balloon segment, e. one of said closed ends of said excision balloon segment being a distal end and having a distal depression in the shape of a circular slot around said longitudinal axis of said excision balloon segment, f. said circular slot having a predetermined internal shape and circumference with an apex pointed toward the other of said closed ends, and an open side on the surface of said distal end of said circular excision balloon device, g. said excision balloon segment being made of material differentially compliant to fluid pressure produced inside said excision balloon segment for causing said excision balloon segment to assume a predetermined shape in response to a predetermined amount of internal pressure, h. said excision balloon segment, when in a semi-inflated state, being of a circumference to press tightly against the inner circumference of said clamping catheter device, and with sides of said depression being almost parallel, i. a circular serrated blade segment permanently attached said to said apex of said depression and enclosed by said side of said depression of said clamping catheter device, j. said excision balloon segment, when in the fully inflated state, being of a circumference to press tightly against the inner circumference of said clamping catheter device, and with apex of said depression close to said distal end of said excision balloon segment, thus placing said circular serrated blade outside said distal end of said circular balloon segment by a distance sufficient to cut through said wall of said first body tube, k. said excision balloon segment, when in the deflated state, being of a circumference somewhat smaller than said circumference of said clamping catheter, but larger than the circumference of said circular serrated blade segment, l. said circular serrated blade segment having a cutting edge and a shape and circumference approximately equal to a preselected shape and circumference of the end of said graft tube to be anastomosized to said excised opening in the side of said first body tube, m. said circular serrated blade having a width sufficient to cut through said wall of said first body tube, n. said circular serrated blade having a plurality of serrations in said cutting edge such that the force of pushing said circular serrated blade is distributed to points on the circumference of said circular serrated blade unequally, thus applying full force to each successive increment of tissue being cut by the portion of the blade in contact with that increment of tissue, o. a cruciform dart segment having a generally conical shape with a sharp point on a distal end thereof, p. said cruciform dart segment being of sufficient bluntness on the proximal side to draw said disc of excised tissue back through said non-collapsing tunnel for disposal outside the body, q. a dart guide wire attached to said cruciform dart segment, said dart guide wire having sufficient stiffness to push said cruciform dart segment through said wall of said first body tube, and r. an inflation tube for inflating and deflating said excision balloon segment, said inflation tube being attached to said excision balloon segment and held within said excision catheter segment, whereby said circular excision device (a) cuts a disc of tissue from said wall of said first body tube of the same circumference as that of the graft tube being anastomosized there, (b) removes said disc of tissue, thus providing a opening in said first body tube of a shape and size to match the tissue on said graft tube for optimal growth potential and leak resistance.
 85. A circular push-blade balloon device for slitting an opening in a wall of a first body tube for anastomotizing a graft tube to said opening at an angle from about 30 to 90 degrees, comprising: a. a circular push-blade balloon segment having a longitudinal axis and a cylindrical shape with closed ends, b. said circular push-blade balloon segment having a proximal end and a distal end, c. said proximal end of said push-blade balloon segment generally intersecting the longitudinal axis of said circular push-blade balloon segment at about 90 degrees, d. said distal end of said push-blade balloon segment generally intersecting the longitudinal axis of said push-blade balloon segment at an angle approximately equal to the predetermined angle at which said graft tube is to be anastomosized to said first body tube, e. a push blade catheter segment having a tubular shape with distal and proximal ends, f. said distal end of said push blade catheter segment being attached to said circular push-blade balloon segment through said longitudinal axis of said circular push-blade balloon segment, g. said distal end of said push-blade balloon segment having a depression in the shape of a slot, h. said depression having a predetermined internal shape, with an apex pointed toward said proximal end of said excision balloon segment, and an open side on the surface of said distal end of said circular push-blade balloon device, i. a straight blade having a sharp edge on one side and a blunt side opposite, j. said blunt side of said straight blade being permanently attached to said apex of said depression in such a way as to support said straight blade from tipping toward either side of said depression, k. said straight blade having a width sufficient to cut through said wall of said first body tube, l. said circular push-blade balloon segment being made of material differentially compliant to fluid pressure produced inside said circular push-blade balloon segment for causing said circular push-blade balloon segment to assume a predetermined shape in response to a predetermined amount of internal pressure, m. said circular push-blade balloon segment, when in a semi-inflated state, having a circumference smaller than said circumference of said clamping catheter and said sides of said depression being almost parallel, n. said circular push-blade balloon segment, when in the fully inflated state, being of a circumference to apply sufficient pressure to the inside circumference of said clamping catheter device to accomplish a temporary connection, and extend said apex of said depression close to said distal end of said circular push-blade balloon segment, thus placing said straight blade outside said distal end by a distance sufficient to cut through said first body tube, and o. an inflation tube for inflating and deflating said push-blade balloon segment, said inflation tube attached to said push-blade balloon segment and held within said push-blade catheter segment, whereby said circular push-blade balloon device can slice an opening in said first body tube of a length to match the predetermined circumference of said graft tube being anastomosized at a predetermined angle, and (b) being attached by pressure to said clamping catheter device, the distal annular balloon of said clamping catheter device moves through said opening as said opening is being made and thus is in position to be inflated to clamp said opening before blood has time to escape through said opening, thus exposing the intimal layer of tissue for joining with the intimal layer on the end of said graft tube for maximizing growth rate and leak-resistant anastomosis.
 86. A tubular push-blade balloon device that is mountable on a holding balloon device and that has a blade that is positioned inside when said tubular push-blade balloon device is in a semi-inflated state and that is pushed outside when said tubular push-blade balloon device is in the fully-inflated state, comprising: a. said push blade balloon device having a push-blade balloon segment of a tubular shape with closed ends, b. said push blade balloon segment being mounted on said holding balloon device and held by fingers of said holding balloon device, c. said push-blade balloon segment having a V-shaped depression open on a side opposite said holding balloon device, said depression having an apex near said holding balloon device, d. a straight edge push-blade having a blunt end and a blunt side, and being in the shape of two rectangles attached end-to-end by a hinge such that the two rectangular halves will fold together and overlap, e. a body of material along said apex of said depression sufficient to attach said blunt side of said straight edge push-blade in such a manner as to resist said straight edge push-blade tipping toward either side of said depression, f. said push blade balloon segment being of sufficient depth and length to enclose said two halves of said straight edge push-blade, said two halves being attached at said apex of said depression, g. said tubular push-blade balloon segment, when in a fully inflated state, being shaped and positioned to cause said apex of said depression in said tubular push-blade balloon segment to expel said straight edge push blade through the open side of said V-shaped depression, h. said push-blade balloon segment, when in a semi-inflated state, having essentially the same shape and dimension as in said fully inflated state, except said depression is entirely within said push-blade balloon segment, thus providing protection for said cutting edge of said straight edge blade, i. said straight edge push-blade being of sufficient width to cut through a predetermined thickness of a wall of said body tube, j. said blunt end of said straight edge push-blade being on the end of said tubular push-blade balloon segment, where said push-blade balloon segment forms a predetermined acute angle between about 30 to 60 degrees with said body tube, k. said tubular push blade balloon device and said body tube being oriented so that said acute angle is in the direction of a forward force vector produced by pushing said tubular push blade balloon device against said body tube, another force vector being normal to said second body tube, l. said blunt end of said straight edge push blade being sufficiently wide so that cutting in the direction of said forward force vector against said acute angle does not inhibit cutting in the direction of said force vector normal to said body tube, so that when said straight edge push blade cuts said opening in said body tube, said blunt end slides into said opening, m. said push-blade balloon segment, in the deflated state, being folded in its center with said straight push-blade folded side-by-side, n. a fluid-carrying tube for inflating and deflating said push-blade balloon segment, and o. a push blade guide wire attached to said two halves of said straight edge-push blade such that pulling said push-blade guide wire pulls said two halves together and draws said halves out of the body, whereby (a) an opening in a side of said body tube is cut to the correct size for being anastomosized with a predetermined size and shape of one end of a graft tube at an angle between about 30 to 60 degrees, (b) said blunt end of said straight edge push-blade, said push-blade balloon segment, and said distal holding balloon on which said push-blade balloon segment is mounted will be pushed through said opening as said opening is cut, thereby (c) filling said opening and thus inhibiting blood from escaping from said opening until a permanent seal can be put in place, and (d) exposing the layers of tissue around said opening to the layers of tissue of said graft tube to be anastomosized with said opening, thus promoting optimal growth of the anastomosis.
 87. The tubular balloon push-blade device of claim 86 wherein said sharp edge of said straight edge push blade deviates from being straight in the ends of said straight edge blade curve up to the center of said sharp edge so that said center touches said body tube before said ends such that the full force of pushing said sharp edge through tissue is distributed to successive points along said cutting edge as they come in contact with said sharp edge in successive instants of time, whereby a smaller amount of force is required to cut through said tissue with respect to that required when the entire length of tissue is addressed simultaneously.
 88. The device of claim 86 wherein said straight edge push blade is constructed of permanent magnet material.
 89. A slicing blade device for cutting art opening of predetermined length in a side of a body tube for an anastomosis between said body tube and a preselected size graft tube at a preselected angle between said body and graft tubes, comprising: a. said slicing blade device and a distal holding balloon device having a plurality of fingers, said slicing blade device capable of being attached to said distal holding balloon device and held by said fingers of said distal holding balloon device, b. said slicing blade device having a housing of a generally cylindrical shape with closed ends, c. said cylindrical housing encircling and defining a lumen or tunnel, d. said cylindrical housing having a longitudinal slot providing an opening from said tunnel to the exterior of said cylindrical housing, e. said tunnel being angular in cross-section, f. a cart having the same angular cross-section as said tunnel and sized to slidably move through said tunnel, g. said cart having a slot that is shorter than said longitudinal slot and that is aligned with said longitudinal slot in said cylindrical housing, h. a blade pivotally mounted in said cart, said blade having sufficient length to extend through said shorter slot, beyond said longitudinal slot, and through said side of said body tube, l. a pulling wire attached to said blade so as to raise said short blade in said cart in response to a pull on said pulling wire and pull said cart and said blade through said tunnel, k. a bar mounted on said cart so as to stop said blade when said blade is pulled from initial down position to upright position in said cart by said pulling wire, l. a hinge on said bar that allows said bar to swing from a position of stopping said blade to a position of releasing said blade, m. a protuberance in said tunnel and a lever on said cart that releases said bar when engaged by said protuberance, thereby causing said blade to fall sharp edge down, n. said tunnel having an end chamber, o. a pair of hinged doors near said end of said tunnel, said hinged doors being arranged to swing to allow said cart to enter said end chamber of said tunnel after said blade has fallen, said pair of hinged doors being arranged to swing in the direction allowing said cart to enter but not to swing in the opposite direction to release said cart, p. an end pulley at the end of said end chamber, said pulling wire extending or wrapped around said end pulley for providing a change in direction of about 180 degrees for said pulling wire, q. a longitudinal passage in said cylindrical housing for containing said pulling wire after said pulling wire has changed direction around said end pulley, r. a mid-point pulley at the end of said longitudinal tunnel located near the mid-point of said cylindrical housing, said pulling wire wrapped or extending around said mid-point pulley to change direction by approximately 90 degrees, s. an opening in said cylindrical housing located near the midpoint of said cylindrical housing for said pulling wire to pass through said cylindrical housing, t. said slicing blade device being held by said distal holding balloon device for enabling said distal holding balloon device to enter said body tube immediately as said slicing blade device slices an opening in said body tube, thus inhibiting blood flow though said opening, u. said cylindrical housing of said slicing blade device having two halves connected by a hinge near the midpoint of said cylindrical housing, v. a locking lever holding said halves of said cylindrical housing together, w. a mechanism for unlocking said locking lever, said mechanism being positioned and arranged so that said mechanism releases said locking lever when said cart enters said end chamber, and x. said two halves of said cylindrical housing being capable of folding together on said hinge when said locking lever is in a released state, whereby (a) said opening in said side of said body tube is made of the correct size for being anastomosized with a predetermined size and shape of one end of said graft tube, (b) as said opening is cut said cylindrical slicing device and said distal holding balloon on which said slicing blade device is mounted enter said opening thereby (c) filling said opening thus inhibiting blood from escaping until a permanent seal can be put in place, and (d) said opening exposes the layers of tissue around said opening to the layers of tissue of said graft tube to be anastomosized with said opening, thus promoting optimal growth of said anastomosis.
 90. The slicing blade device of claim 89 wherein said pulleys are molded aspects of said cylindrical housing that present the same shape to said pulling wire as said pulleys and said molded aspects are coated with a slippery substance that enables said pulling wire to slip over said molded aspects of said cylindrical housing of said slicing blade device.
 91. A swinging cutting arm device with a cutting arm that can swing in an arc for slitting an opening in a side of a body tube so said opening can be anastomosized to one end of a graft tube, comprising: a. said swinging cutting arm device being mountable on a holding balloon device, b. said swinging cutting arm device having a longitudinal chamber defined by a cylindrical housing or encircling wall, c. said cylindrical housing having a base and a longitudinal opening to said longitudinal chamber, d. a swinging arm mounted inside said longitudinal chamber, e. said cylindrical housing having a longitudinal tunnel parallel to said longitudinal chamber with a wall between said longitudinal tunnel and said longitudinal chamber, f. an embedded rod extending through said longitudinal tunnel and slightly beyond one end of said longitudinal tunnel, e. a short spring connected to the extended end of said longitudinal rod and said swinging arm, g. said swinging arm having an embedded cutting blade with a sharp edge facing said longitudinal opening, h. a pulling wire attached to said swinging arm in such that when pulled, said cutting arm swings in an arc through said longitudinal opening, i. said pulling wire, when released, being arranged to allow said swinging arm to return to its location in said longitudinal chamber by action of said short spring, j. an exit tunnel through said cylindrical housing from said longitudinal chamber to said base of said cylindrical housing, k. an enlarged section in said exit tunnel containing a double pulley comprising two pulleys facing each other, l. said pulling wire being threaded through said exit tunnel and wrapped around said double pulley so that said pulling wire changes direction as said swinging arm swings through an arc, and m. said double pulley having a plurality of axles embedded in said thick wall so that said pulling wire cannot escape the groove made by said facing double pulleys, whereby said opening may be slit in said body tube for an anastomosis with said end of said graft tube.
 92. The swinging arm cutting device of claim 91 wherein said cylindrical housing is shaped like said double pulleys and coated with a slippery substance such that said pulling wire will slide rather than roll.
 93. The swinging arm cutting device of claim 91 wherein said cylindrical housing of said swinging arm device is suitable for mounting in said tunnel of said holding balloon device with said longitudinal opening, of said swinging cutting arm device being fully exposed.
 94. An explorer guide wire device for making a curved path between two points when a body part is positioned in a straight path between said two points, said two points being the preselected sites for anastomosis on a first body tube and on a second body tube, comprising: a. a guide wire having a J-shaped distal end, b. said J-shaped distal end of said guide wire being of a length sufficient to extend between said preselected sites, c. said J-shaped distal end made of material that retains a bent shape until physically re-bent by a user into a different shape, d. a plurality of radiopaque markers, viewable on fluoroscopic screens, e. said plurality of radiopaque markers being attached to said guide wire longitudinally and annularly, and f. a screw tip on said J-shaped distal end for anchoring said guide wire device to said second body tube, whereby said explorer guide wire device may (a) be shaped by a user to match a curved path from a preselected site on a first body tube to a preselected site on a second body tube that passes around a body part intervening in a straight path, (b) be reshaped as necessary to correct initial estimates of said curved path according to observations of radiopaque markers on a fluoroscopic screen and (c) be anchored at said preselected site on said second body tube and (d) thus be available for guiding catheter devices from said preselected site on a first body tube to said preselected site for anastomosis on said second body tube.
 95. The explorer guide wire device of claim 94, further including: a. a radio frequency receiver located in said screw tip of said explorer guide wire device, b. a target guide wire with a distal tip, being advanced by an operator to said predetermined site for anastomosis on said second body tube, c. a radio frequency transmitter in said distal tip of said target guide wire d. said radio frequency transmitter and said radio frequency receiver being of the same radio frequency, e. equipment outside the body for energizing said radio-frequency transmitter, receiving and comparatively displaying the strength of signals from said radio-frequency receiver, f. said radio frequency receiver being connected by said explorer guide wire to said equipment, and g. said radio frequency transmitter connected by said target guide wire to said equipment, whereby an operator can use said display equipment to compare the strength of a received signal transmission at various locations of said explorer guide wire screw tip as an aid to bringing said explorer guide wire screw tip into proximity with said target guide wire tip at said preselected site for anastomosis on said second body tube.
 96. The explorer guide wire device of claim 95, further including: a. a second radio frequency transmitter located close-to said radio frequency transmitter in said distal tip of said target guide wire, b. a transmitter delay line connecting said second radio frequency transmitter to said radio frequency transmitter, c. a second radio frequency receiver located close to said radio frequency receiver in said screw tip of said explorer guide wire, d. said second radio frequency receiver and said radio frequency receiver being connected to energizing and receiving equipment outside the body, e. all radio frequency transmitters and receivers being of the same radio frequency, f. said energizing and receiving equipment outside the body having the capability to select, measure, compare and display returns from said second radio frequency receiver and said radio frequency receiver, whereby an operator using displays outside said body is aided in bringing said explorer guide wire into alignment with, as well as proximity to said target guide wire at the target predetermined site for anastomosis on said second body tube.
 97. A radio frequency device providing an aid to a user for bringing a delivery tube device into proximity and alignment with a preselected site for an anastomosis on a body tube, comprising: a. four radio frequency receivers located a distal end of said delivery tube device, b. said four radio frequency receivers being spaced approximately equidistantly on the short and long axes around said distal end of said delivery tube device, c. a target guide wire with a distal tip, d a pair of radio frequency transmitters located in said distal tip of said target guide wire, e. a delay line between said pair of radio frequency transmitters, f. all radio frequency transmitters and receivers being tuned to the same radio frequency, g. equipment outside the body for energizing said pair of transmitters, receiving, selecting, measuring, comparing and displaying received signals from said four receivers so as to provide a predetermined indication when all are of equal strength, h. said pair of radio-frequency transmitters being connected to said equipment outside the body by said target guide wire, and i. said four receivers connected to said equipment outside the body by connecting wires etched in said delivery tube device, whereby strength of received signals from each of said four receivers are selected for measurement and comparison of strength of received signal and displayed to aid a user in moving said delivery tube device to be in proximity and aligned with said pair of transmitters in said distal tip of said target guide wire, said location being at the predetermined site for anastomosis on said body tube when said target distal tip is located at said predetermined site.
 98. A device for drawing a magnetized cutting blade into proximity and alignment for cutting an opening in a body tube, comprising: a. a target dual guide wire with a tip on a distal end thereof, b. said tip of said target dual guide wire being advanced by an operator to a preselected site for an anastomosis on a body tube, b. a magnetized bar mounted on said distal tip, c. a magnetized cutting blade on a cutting device, and d. said magnetized bar being connected by said target dual guide wire to a reversible source of direct current electric energy outside a body, whereby said magnetized bar is capable of drawing said magnetized cutting blade toward said magnetized bar thus aiding in placing said magnetized blade in the correct position and alignment for cutting said opening in said body tube for an anastomosis and rejecting said magnetized cutting blade when said direct current electric energy is reversed. 